Integrated Head and Neck Tandem-Bracing Device for Protective Helmets

ABSTRACT

An Integrated Head and Neck Tandem-Bracing Device for Protective Helmets is introduced for hazardous activities such as hockey, American football, and others which require safety helmet protections against head impact trauma. The default vulnerability in such hazardous events is the lack of solid securitization of the neck of helmet wearers during such activities. The novel art is designed to protect the wearer against external impact injuries to the head but essentially to the extent the neck is solidly braced, in-tandem, between helmet and torso, at instance of an impinging impact. The novel device presumes optimal protections based upon safeguarding the integrity of the central nervous system: head, neck, and all vertebrae, the torso. This standard of care and the novel technology are integral for maintaining vital safety measures which have been unanticipated by conventional equipment.

This is a Continuation-In-Part application referencing Application No. 14/679,001 Filed Apr. 5, 2015 further referencing International Application PCT/US2014/036261 with Filing Date: Apr. 30, 2014, further claiming benefit of Provisional Application 61/817,484 Filed Apr. 30, 2013

BACKGROUND

Field of the Invention

The invention presented herein relates generally to requirements for a head, neck, and torso bracing framework component as protective gear against bodily injury which would be needed in the fields of often hazardous sports and competitive events. More specifically, it is relevant to a component which affords a wearer relative optimal protections against injurious impacts to the head, relevant to neck vulnerabilities, and the torso thus inhibiting and delimiting these often traumatic impacts in the fields of both athletic tackle sports such as hockey and American football, in addition to motor vehicle race course competitions and others.

BACKGROUND

Description of Prior Art

This novel idea is a radical change from the conventional use of both a helmet's hardened outer shell, a supposedly protective hardened inner abutment, and even the practice of “protection by padding,” of protective helmets. It is a unique apparatus which seeks to effectively circumvent injuries to the head due to impinging impacts from field-tackle collisions, in sports, such as in: rugby, lacrosse, cycle vehicle racing, hockey, and American football. The manufacturers of protective helmets of both hockey and American football claim to provide products that are up to standard for safety. There are several innovations which are stated to be, more or less, more effective in safety than others. Manufacturer's state these in the media as innovative benefits. Some are related herein. The use of Rate-Sensitive Foam is “one of the technical improvements.” according to the designers. The foam stiffens more under a harsher impact; this, in itself, is counterintuitive since compressed cushioning, as compacted by the head at moment of an impact, will alter its state into a hardened material against the inner wall of a helmet. Another. “Slip-Pane Technology,” (also multi-directional Impact protection system) is supposedly capable of absorbing rotational impact. Its Dual-Shell feature has a surface which is slick-skinned enough to allow roll-away of an impacting force. One of the designs utilizes a five-sided indentation on the crown of the helmet; it is stated to cause certain impacting forces to be absorbed and dispersed and not go to the head. There is no structurally superior novelty in these designs as far as achievable protections are concerned. Oncoming impacts do not seek out one discrete target on an adversary's helmet, and rotational hits, for any given impact are bound to carry far more G-forces than to roll away from one slick surface though supported by a sub-surface. The “cantilever is introduced to allow the helmet.” according to designers. “to flex more while maintaining an overall stiffness. Thick padding behind the movable area doesn't allow it to move much, but just enough in an area where players “can take big hits.” Solutions such as these are ineffective upon comparison with scientific fact and logical implementation for total protections of the CNS which necessarily entail a tandem bracing relationship between head and torso at moment of any force of impact, whether moderate or massive. Wordings such as “futuristic design” and “the latest in head protection” are used. None of the manufacturers claim an intuitive design structure that focuses on the tandem relationship between the head and torso.

The default vulnerability of all protective helmets is the lack of this bio-mechanical relationship; it continues to exist as a fatal design flaw. The disastrous oversight has proven itself as a deadly consequence to ignorance of, or dismissive evasion of, good and excellent medical science with respect to the integral position of the neck in field tackle sports injuries. Surely the designers must have taken notes on the IHANS device for speed car racing drivers; it is the Integrated Helmet And Neck Support device. These designers are on the right track for pointing up the vital significance of the relationship between the head and neck while in close quarters to the hazards of serious injuries and potential fatal collisions on the speedway where the G-forces are far greater than on the fields of play of hockey and American football.

A manufacturer of hockey protective helmets introduces a new technology which involves using a suspended Tech Liner system with a type of foam, which, according to them, “which is what makes . . . so much different than anything else on the market.” It is further described: “A free-floating system allows the shell of the helmet and liner to move independently upon impact . . . to reduce any additional movement of player's head from both a direct impact and any sort of whiplash type movement . . . high-tech Poron XRD foam with special placement in helmet allows design qualities for impact dispersal, in addition to other features using memory foam.” Another technology deemed to be revolutionary in hockey protective helmets is a linear system designed to disperse direct impact away from a single point on the wearer's head. It compresses immediately and laterally disperses energy. It is stated that this technology “compresses and resets within seconds.”

The constant flow of innovations mention: extra padding, “ . . . concussion reducing technology which adds even more padding,” replacement of “foam padding with an array of air-filled cylinders that compress upon impact by releasing air through tiny holes.” what is called, “large-offset design; in other words, increased distance between the head and the shell in order to make more room for extra padding,” a helmet which “claims to be the lightest helmet on the market. Its shell includes Kevlar and carbon fiber; its padding consists of a single layer of a proprietary composite whose makeup won't be disclosed, by . . . until it is patented.” The findings may appear appealing theoretically, or in the laboratory; however, the Integrated Head and Neck Tandem-Bracing Device responds to the real challenges with logical solutions, not losing sight of the fatal tragedies regularly played out in real time on the field in global arenas. This new technology presumes all the objective solutions of prior art as may be determined by their design focus; of course, their earlier design objectives had novel attempts at protections for overall safety of those on the fields of play; however, without the new standards for safety, with acknowledgement to the vulnerability of the neck, and further the CNS, debilitating injuries are likely to continue.

The above reduces both linear and rotational accelerations;

-   -   1. Let the body distribute the weight—not the head alone! Proof:         A helmet. “alone,” is not adequate for safety; it requires a         connection with an anchoring apparatus, a tandem neck-spanning,         bracing, device.     -   2. Solves Rotational Forces: IHNTBD braces against rotational         accelerations.         One company introduces a helmet that relies on what's called         large-offset design; in other words; increased distance between         the head and the shell in order to make more room for extra         padding. One of the Drop Test Systems used for athletic         equipment—Once used a crash test dummy head and neck to simulate         impact forces for rotational responses to repeated 12-mi/hr.         impacts.

Objects and Advantages

Other than the benefits of the Integrated Head and Neck Tandem-Bracing Device described above, several objects and advantages are to provide An Integrated Head and Neck Tandem-Bracing Device for Protective Helmets:

-   -   a. which, upon impact, immediately braces itself while         inhibiting the force of impact from reaching the user/wearer by         use of an immediate response mechanism utilizing unique bracing         facilities;     -   b. which can protect a wearer's head from the devastating         injuries that can inflict a non-protected person with immediate         impact trauma to the head, but more specifically to the neck         (due to its tandem relationship between head and upper torso,         thereby having positive ramifications with regard to even the         extremities—considering the integrity of the central nervous         system. The CNS, reliant upon the tandem significance of the         neck, has been overlooked as a factor in the neurological         problems in the design of protective helmets, whether relevant         to sports activities such as rugby, lacrosse, hockey, and         American football; but further, retracting the torso impact         component, to rodeo bull riding sports, horseback riding,         skateboarding, and even bicycle riding;     -   c. whose operation for immobilization of the protection helmet         entails mechanical, coordinated, and corresponding mechanisms         including several pneumatic compression processes for         effectuating cessations of movements of the neck due to an         external impact, or jolt, to the protective helmet and/or due to         a fall to the ground, a time-intervening, bracing action, at         split-second interval prior to an, otherwise, injurious jolt to         the head or torso, would prevent such jolt by such intervening         action;     -   d. whose efficiency involves delimiting of torsion, turning,         stretching, and bending movements of the neck of the wearer at         onset of a potentially injurious impact event to protective         helmet of the wearer;     -   e. whose bracing designs structures are sufficiently predisposed         to momentarily impede all movements of the neck, (thus the head)         at moment of a jolting impact from any direction: right angle,         lateral, diagonal, head on, frontal, dorsal, head-on shoulder,         rotational, head-on crown of helmet, side, rear of helmet, falls         from a height, (head to ground/right angle shoulder to ground)         etc. for about as long as exterior force is maintained, or held;     -   f. whose anchoring structure for bracing and deflection of         external adverse impacts is due to immediate, split-second,         locking of movement of the helmet thus blocking an injurious         jolt; such novel dynamics address and/or resolve the ongoing         concerns involving neurological health liabilities pertaining to         the typical protective helmets, particularly with respect to         hockey and American football;     -   g. whose helmet component, (and shoulder component) once struck         externally, would cause it to brace itself with respect to the         upper torso, (shoulders) serving as substantial anchoring         structure against any movement consequent to an impact; the         neck, not subject to “direct” hits, is designed to “brace by         default” of an impacting jolt to the helmet since it is         functionally contiguous to the tandem collar-shoulder bracing         segment as a corresponding dual-component tandem response         operation;     -   h. whose introduction is designed to replace the conventional         protective helmets and related protective gear used primarily         both, in sports activities such as ice hockey and American         football;     -   i. whose overall resiliency will prove to be a constant reminder         that, at least, hockey and American football may be enjoyed         safely;     -   j. whose overall protections cover not only the head but also         the neck, essentially, and now, with added protections for the         torso, as a new design component for such extended protections         from injurious impacts signifies the superior value of this new         technology in that its design presumes that the neck is vital         with respect to the integrity of the CNS. This fact has been         overlooked in the customary design flaws of present conventional         sports protective gear;     -   k. whose inertial mass weight as the “force of impact         deflection” to the head or torso as secured to the device, would         take the “distributed” shock force of the jolt, not the wearer's         head and/or neck thus delimiting any overall adverse force that         may remain;     -   l. which, additionally, features an Impact Damping/Suppression         Cradle; this is particularly helpful against adverse impacts         with respect to falls to the ground, in addition to lateral         impacts:     -   m. whose structural design has an interior helmet-to-head         harnessing apparatus, which accommodates freedom of movement for         a protective helmet to precisely coordinate with wearer's head         movement, further providing that any exterior movements, or         impacts, (in contrast to that of the harnessing apparatus         itself) would cause a bracing, locking, event for the device;     -   n. that is designed for heavy duty twists, turns, stretching,         bending, and forceful impacts, being sufficiently durable so as         to be capable of being subjected to the most rigorous physical         demands made upon it;     -   o. whose facility is sufficiently predisposed to momentarily         impede all movements of the neck, (thus the head and torso) upon         impact from any direction: right angle, rotational, lateral,         diagonal, head on, frontal, dorsal, head-on crown of helmet,         side, rear of helmet, as well as falls to the ground sustained         directly by front or rear helmet, or by a shoulder;     -   p. that is designed to cushion injurious jolts by bracing,         dividing, and distributing the forces of impinging impacts         throughout the “consolidated” inertial mass of the braced object         which being the mass weight, (not the body itself) of the         wearer/user of the device.

SUMMARY

A unique design as body protective gear is herein provided. American football's current association with media reports of repeated impact trauma, leading to concussions and long-term health issues, now calls the sport into question. This new apparatus, in part, addresses the problem of this dilemma with a novel solution for the players as well as a welcome amenity for the sport itself. The essential benefit of such technology may be thought of as an “exo-skeletal firewall” structure designed to arrest any exterior jolt to the apparatus, dividing and distributing its force of impact between two colliding objects, based on physical laws of inertia, immobilizing any movement of the neck, (head) and torso from any motion upon onset of an exterior impact to the protective helmet, or to the vest/torso bracing component of the structure. This immobilizing, bracing, feature is the revolutionary benefit making this novel apparatus superior to all other such protective equipment since its bracing effect, and in fact, causes an incoming, and potentially-injurious, impact to be met with a counterbalance of mass weight but which also circumvents dangerously engaging the independent and exclusive mass weight of the head, alone, (as by default presently) but with that of the entire body—as a consolidated, unified, object of resistance thus following the first and second laws of motion as given by Sir Isaac Newton. The physical principles of inertia, friction, and pneumatic compression comprise the structural design and overall concept of this new technology referencing the vulnerable bio-mechanical tandem relationship between head and torso. The concern is not with the flexible movement of the torso, per se, but with the split-second capability of the device to prevent a twisting or bending movement between the waist and shoulders, and the neck, (by a tandem locking event) with respect to an “anchoring capacity” of the torso, further providing protection of the head within the helmet, first of all but also to the torso against whiplash for further overall protection of the central nervous system, CNS.

In the typical protective helmet, no matter what configuration or amount of layering of cushioning/padding materials is utilized against head impact trauma. “more is not better” since the problem is not resolved; stuffing more padding, of any consistency, into the helmet would prove to be no less injurious than at present since the head would still sustain the shock from a more-than-moderate impact though there appears to be a “sufficient” complement of cushioning. This would be due to the closeness of the head to the “compressed” (thus hardened) interior-surface padding of the protective helmet at instance of an exterior impact to the helmet. Technically, the limited distance between the inner wall surface of the helmet and the head, being what it is, is a guarantee that head impact trauma will occur—no matter the type, measure, or consistency of cushioning. Nothing causes the compression of the cushioning material other than the kinetic mass force of an impinging impact object against the inertial mass weight of the head which is being impacted against the internal wall of a protective helmet at moment of the striking of an impinging external object impact; additionally, the hardness or softness of the helmet shell does not matter—for physical reasons explained within.

Such sequence allows an effect that is too slight for cushioning protection; it would be nearly the same as if the head were to be directly struck, without any cushioning at all since both the padding and cushioning would then “not” be pliable but hardened solid due to condensing physical depressions against them. The dilemma with most of the protective helmets examined, presently on the market, that, since padding and cushioning presently entail the “primary” component, per se, against head impact injuries with respect to sports protective helmets, such injuries, now widely reported in the news media will likely continue. Actually, helmet manufacturers would prefer such a simple solution as cushioning and padding alone; however, a revolutionary design is now available that makes helmets more safe.

How it Works: (Outline) Physical Law—Isaac Newton's Laws of Motion (Summarized)

-   -   1. First Law: “Forces that change an object's motion must first         overcome its (the object's) inertia.”     -   2. Second Law: “A force, acting on an object, produces an         acceleration which is equal to the force divided by the mass of         the object.”     -   3. Pneumatic Cylinder Compression (rod/piston/valve)     -   4. Pneumatic Tubular Compression,     -   5. FRICTION: (Clinching/Bracing),     -   6. RETRACTION PROCESSES,     -   7. Deceleration of Impinging Forces by Fractional Distribution:         Transference of Mass Weight of a force exerted by an impacting         object to (across) tandem device.     -   8. Attenuation of Impacting Force,     -   9. Cushioning/Padding only at top of helmet for against crown of         helmet for downward force of impinging impact. Padding for sides         of helmet against lateral hits would introduce potential for         compressed, compacted, condition of such materials at moment of         an impact thus assuring.

DRAWINGS

Page 1

FIG. 1 shows a frontal perspective representational model view of the relationship between a typical protective helmet and a wearer's head. It indicates a moment-of-impact event and the resulting effect against the wearer's head when unprotected by the novel device:

Page 2

FIG. 2 also shows a frontal perspective representational model view of the relationship between a protective helmet and a wearer's head as harnessed by the novel device but without an impacting event:

Page 3

FIG. 3 also shows a frontal perspective representational model view of the relationship between a sports protective helmet and a wearer's head but utilizing the novel invention herein against exterior impact to the protective helmet; two of the bracing mechanisms are shown here: one indicated referenced by 16, the other referenced by the corresponding actions among 26, 28, and 34:

Page 4

FIG. 4A is a partial anterior perspective of the Integrated Head and Neck Tandem-Bracing Device with its upper torso harnessing component and an exemplary protective helmet, not showing the anterior shield:

Page 5

FIG. 4B is a partial posterior perspective of the Integrated Head and Neck Tandem-Bracing Device with its upper torso harnessing component, an exemplary protective helmet, and a segment of the pneumatic compression/retraction apparatus;

FIG. 24E-1 is the Lateral (Shoulder) Impact Compression/Retraction Device; FIG. 24E-2 is the device of FIG. 24E-1 but slightly enlarged to exhibit the relevant identity reference numbers.

Page 6

FIG. 20 is a side view of a retraction/friction brace rod and its friction jacket/sleeve through which its friction brace rod is shown to be passing;

FIG. 21 shows the retraction friction brace rod sleeve in its closed, clenching, aspect;

FIG. 22 illustrates the open aspect of the friction jacket/sleeve in its open, non-clenched aspect, indicating non-retraction cord/wire mode and free movement of head/helmet;

FIG. 23 illustrates the layout for the retraction mechanism of the retraction cord/wire, not showing the lever, the friction stabilizing rods nor the jacket/sleeve in its non-retracted aspect, as is the case here, indicating free voluntary movement of the head/helmet;

Page 7

FIGS. 10a-10c -1 and 10 d-10 f illustrate several structural positional mode aspects taken by the stabilizing retraction/bracing friction rod units as coordinated with the natural movement positions of the wearer's head/helmet;

FIG. 11 shows an approximate perspective view of a scaled-down depiction of how the tandem neck-spanning device would appear with the three clinching/bracing units;

Page 8

FIG. 16 depicts an end view of one of the side stabilizing retraction/bracing friction rod units illustrating, here a side aspect showing how the retraction friction/brace rods correspond in-tandem;

FIG. 17 depicts one of the stabilizing retraction/bracing friction rod units illustrating here a frontal aspect showing how the retraction rod elements correspond in tandem;

FIG. 18 shows one of clinching/retraction units in non-clenched, non-bracing, mode of the tandem neck clinching/bracing device;

FIG. 19 shows one of the retraction units in clenching, bracing, mode of the tandem neck clinching/bracing device;

Page 9

FIG. 5 illustrates a perspective end view of one of the Integrated Head and Neck Tandem-Bracing Device’ stabilizing retraction/bracing friction rod units, including its foundational anchoring support and peripheral module cushioning supports;

Page 10

FIG. 6 is an exploded side view of the general structural design components of one of the, at least three, retraction/bracing friction rod units;

Page 11

FIG. 7A and FIG. 7B show two generalized views of singular neck stabilizing units/modules as may be seen from the interior of a protective helmet; the first 7A is unshielded; the other 7B is shielded with a padding-like material;

Page 12

FIG. 9A is a grossly generalized grouped perspective view of three of the units of the Integrated Head and Neck Tandem-Bracing Device as enclosed within a protective helmet; and FIG. 9B is the same grouped perspective view of three of the neck stabilizing units of the Integrated Head and Neck Tandem-Bracing Device but as seen from rear exterior of a protective helmet and as shielded by their veneer covering;

Page 13

FIG. 24B indicates the retraction aspect as depicted in FIG. 18 showing one of, at least two, neck stabilizing units in non-clenched, non-bracing, mode of the Integrated Head and Neck Tandem-Bracing Device;

FIG. 24C indicates the retraction aspect as depicted in FIG. 19 showing one of, at least two, “side” retraction units in clenched, bracing, mode of the Integrated Head and Neck Tandem-Bracing Device;

FIG. 24D shows the unique structural aspects of the rear retraction unit, the Master Retraction Unit, in non-retraction mode; rather than show wire/cord for purposes of pulling upwards, it depicts here rigid push-rod connections for both pushing downwards and “being pulled” downwards to effect a retraction event;

Page 14

FIG. 24A, FIG. 24B, FIG. 24C, and FIG. 24D are depictions of the tubular pneumatic compression unit FIG. 24A of the pneumatic compression/retraction apparatus, the left side friction/retraction unit FIG. 24B, the right side friction/retraction unit FIG. 24C and the rear friction/retraction unit, Master Retraction Unit respectively FIG. 24D, of the Integrated Head and Neck Tandem-Bracing Device;

Page 15

FIG. 8A depicts an un-extended push rod (121 a) for non-retraction, non-bracing, mode of the rear friction/retraction unit;

FIG. 8B depicts an extended push rod (121 a) for retraction/bracing mode of the rear friction/retraction unit:

Page 16

FIG. 32A depicts a tube containment/constricting element for the tubular pneumatic compression unit;

FIG. 32B depicts a tube containment/constricting element for the tubular pneumatic compression unit; it indicates here an exterior impacting object coming either from above the protective helmet or below the protective helmet:

FIG. 32C depicts a tube containment/constricting element for the tubular pneumatic compression unit; it indicating here an exterior impacting object proceeding from the left of the protective helmet 75 b indicating a lateral jolt from left;

FIG. 32D depicts a tube containment/constricting element for the tubular pneumatic compression unit in the open position for purpose of attachment to pneumatic compression tube Ref. 53, removal from it, or for extension effect caused by an impact—at opposite side of helmet—causing compression;

Page 17

FIG. 26A depicts a tube containment/constricting element for the tubular pneumatic compression unit being impacted—bringing about compression of compression tube, both, of its own location, and from its opposing element at opposite side FIG. 26B of protective helmet;

FIG. 26B depicts a tube containment/constricting element for the tubular pneumatic compression unit showing effect as explained in FIG. 26A;

FIG. 26C depicts a tube containment/constricting element for the tubular pneumatic compression unit being impacted from above with same structural configuration as in FIG. 32B, both causing compression;

FIG. 26D depicts a tube containment/constricting element for the tubular pneumatic compression unit being impacted from below with same structural configuration as in FIG. 32B and FIG. 26c , both causing compression;

Page 18

FIG. 28A depicts a tube-containment/constricting element, in non-compression mode, in place for both containment and constriction of the tubular pneumatic compression unit;

FIG. 28B depicts a tube containment/constricting element applying constriction compression to the tubular pneumatic compression unit due to a coronal impact initiating from above protective helmet;

FIG. 28C-1 depicts a tube containment/constricting element applying constriction compression to the tubular pneumatic compression unit due to a rotational impact proceeding to the left as observed from the side of the element;

FIG. 28D-1 depicts a tube containment/constricting element applying constriction compression to the tubular pneumatic compression unit due to a rotational impact proceeding to the right as would be observed from the side of the element;

FIG. 28C-2 depicts a tube containment/constricting element applying constriction compression to the tubular pneumatic compression unit due to a rotational impact proceeding to the left as observed from above the element:

FIG. 28D-2 depicts a tube containment/constricting element applying constriction compression to the tubular pneumatic compression unit due to a rotational impact proceeding to the right as observed from above the element;

Page 19

FIG. 29A This is a top-down structural depiction of the positional relationship between the tubular pneumatic compression unit, the rear Master Friction/Bracing Unit environment, and the compression/constriction elements, and the IDSC unit;

FIG. 29B This is a top-down view depiction of the Impact Damping/Suppression Cradle showing the interposition of an impact suppression sheath, and a tier of impact cushion elements for impact suppression;

FIG. 29C This is a top-down view depiction of the Impact Damping/Suppression Cradle showing the central cap covering of a Helmet Support Column and attenuation Node, indicating negligible degree of movement of head due to an exterior impact to the head;

FIG. 29D This is a top-down view depiction of the Impact Damping/Suppression Cradle indicating a forceful exterior impact to the right of the unit but with still negligible movement of head:

Page 20

FIG. 26A This is a right top perspective view of the Impact Damping/Suppression Cradle:

FIG. 26B This is a side perspective view of the Impact Damping/Suppression Cradle;

Page 21

FIG. 27A-1 illustrates a generalized layout view of the relationship between rim, helmet pneumatic tube unit, and the IDSC as seen from the top interior of a protective helmet;

FIG. 27A-2 shows the open end of the pneumatic conduction/compression tube unit;

FIG. 27A-3 is a cut-away lateral depiction of the pneumatic conduction/compression tube unit;

Page 22

FIG. 27B is a top-down view of the pneumatic conduction/compression tube unit and IDSC depicting the unique structural effect consequent to an impact, indicating the forward projection of the helmet and the off-center movement of the Impact Damping/Suppression Cradle thus signifying an impacting jolt;

FIG. 27C a depiction of both a cause and primary effect on both sides of a protective helmet with respect to contributory effects on the opposite side of same helmet;

FIG. 27D a depiction of two effects of an impact to the opposite side of a protective helmet arising from impinging impact of FIG. 27C;

Page 23

FIG. 30 depicts an interior side-view detail representation for a protective helmet, along with the tubular pneumatic compression unit, partial head harnessing component, Impact Damping/Suppression Cradle and stabilizing structure; it does not include a representation of a protective helmet shell itself;

Page 24

FIG. 31A is the underside interior of a protective helmet which shows a section of the primary pneumatic compression tube unit with tube containment/constricting elements, IDSC, Impact Damping/Suppression Cradle, and partial helmet frame attachment structure, and securitization clamps;

31B is a further representation of FIG. 31A but further showing an interior cut-away side view of impact measurement cushions which also facilitate a secondary tier of elements for impact jolt suppression;

Page 25

FIG. 33. This figure is a frontal perspective of the IHNTBD as would be seen worn by the wearer, depicted here are the protective helmet, tandem bracing device, shoulder/torso anchoring structure, front shield unit, and secondary pneumatic compression unit;

Page 26

FIG. 34: This is a rear view of FIG. 33 depicting the corresponding components of FIG. 33;

Page 27

FIG. 25A shows the outer exterior side of the Thoracic Truss Compression Component; FIG. 25B shows the inner side of the Thoracic Truss Compression Component; FIG. 25C depicts an end of a Thoracic Truss Compression Component;

Page 28

FIG. 8A, FIG. 24D, FIG. 24E, FIG. 25B, and Ref. 38 b are structural depictions of the arrangement of the four coordinated retraction and pneumatic compression components of the apparatus; Roman numerals one and two are within the helmet; Roman numerals three and four are exterior to, and below, the helmet;

Page 29

FIG. 35A show two depictions of the torso impact shield: anterior and posterior;

Page 30

FIG. 35D depicts how the front sides of the anterior and posterior impact shields are arranged;

FIG. 35E depicts how the rear sides of the anterior and posterior impact shields are arranged;

FIG. 35B-38 b indicates how it is subject to a steadying event with respect to the element at FIG. 35C-1 b;

FIG. 35C-1 a through 35C-1 e are the various depictions of the Compression Impact Shield Fastener;

Page 31

FIG. 37A through FIG. 37F depict a variety of positional bracing positions as fixed by the Compression Impact Shield Fastener corresponding to the various fixing, bracing positional aspects as determined by the incidental Impact-bracing events;

Page 32

FIG. 38A and FIG. 38B depict the same impact and compression structure except FIG. 38 B is in clinching mode, depicting the CISF prongs as engaged with the back side of an Impact Shield for a bracing event;

FIG. 39A shows a side of IHNTBD being impacted, causing opposite side of IHNTBD FIG. 39B to subsequently brace in reaction;

Page 33

FIG. 40A depicts the left side anterior and posterior shield surfaces with intervening CISF device with its pneumatic compression transfer component in non-engaged, non-bracing mode:

Page 34

FIG. 40B is of the same subject matter as in FIG. 40A on page 33 but indicating here the clinching aspect of the anterior and posterior Impact Shields;

Page 35

FIG. 35A repeats the drawings of page 29; it differs in its reference number in that it is the detached structure, which is comparable to the attached structure FIG. 35B; FIG. 35D shows the side of the Impact Shield dependently attached, front shield and back shield; FIG. 35E shows the the Impact Shield of FIG. 35D in the aspect in which it would be worn by user, FIG. 35D is an open side perspective view of FIG. 35B-1 Pg. 30.

Page 36

FIG. 24E-2-47 f-2 is a referral to a component on page five; shown here is a generalized depiction of a cylinder and piston unit further providing an operational environment for its enclosed piston element.

Page/FIG. No. 1. 1 2. 2 3. 3 4. 4A 5. 4B 24E-1 24E-2 6. 20, 21, 22, 23 7. 10a, b, c-1, c-2, d, e, f, 11 8. 16, 17, 18, 19 9. 5 10. 6 11. 7A, 7B 12. 9A, 9B 13. 24B, 24C, 24D 14. 24A, 24B, 24C, 24D 15. 8A, 8B 16. 32A, 32B, 32C, 32D 17. 26A, 26B, 26C, 26D 18. 28A, 28B, 28C-1, 28D-1, 28C-2, 28D-2 19. 29A, 29B, 29C, 29D 20. 12A, 12B 21. 27A-1, 27A-2, 27A-3 22. 27B, 27C, 27D 23. 30 24. 31A, 31B 25. 33 26. 34 27. 25A, 25B, 25C 28. 8A, 24D, 24E 29. 35A 30. 35B-1, 35B-2, 35C-1a, 35C-2, 35C-3, 35C-4, 35C-1b, 35C-5 35C-6 31. 35A-38-b1, 38-b2, 38-b3, 38-b4, 38-b5, 38-b6 32. 39A, 39B-1, 39B-2, 39B-3 33. 40A 34. 40B 35. 35A, 35D, 35E 36. 24E-2-47f-2 Page/Ref. No. 1. 10 12 14a 16 18 20 22 2. 12 14b 16 20 22 24 26 28 30 31 3. 10 12 14c 16 26 28 30 31 32 34 4. 35a 36 39 41a 44 45 46a 5. 121c 121d 121e 35b 39b 41b 46b 47a 47b 47c-1 47c-2 47d 47e 47f-1 47g 47h-1 47h-2 47h-3 47h-4 47i 47j-1 47j-2 47k 6. 50 62 63 87 88 98 100 101 102 7. 10c-2 8. 44 50 62a 62b 68 70 87 88 104a 104b 9. 42 44 46a/b 50 58 64 72 74 78 80 10. 41 44 48 50 58 60 62 64 66 68 70 11. 41 42 46a/b 52 64 68 82 12. 41 44 46 86 118a 121b 121d 121c 13. 100 101 104a 121b 44 50 62a 62b 68a 68b 70 82 96 14. 44 49 51 53 54 55 56 57a 59a 61 65 67 68c 69 70 73 100 101 104a 121a 121b 121c 121d 15. 121a 121b 44 51 55 57a 59a 59b 71a 16. 53 75a 75b 76 77 79 81 83a 83b 85 89 17. 75b 91a 91b 93a 93b 94a 94b 18. N/A 19. 53 61 65 67 95 96 97b 97a 99 103 138 20. 28 34 21. 53 95 99 103 104b 104a 130 134 142a 22. 53 75b 91b 91c 91a 107 108 109 111 134 142b 23. 105 106 108 110 114 116a 116b 116c 117a 117b 118a 118b 121b 121c 122 24 26 28 35 41 44a/b 53 65 68 24. 28 34 53 65 67 79 85 89 90 104a 106 110 113 125 25. 35a 36 39 41a 44 45 46 131a-1 131a-2 129a 133 136b 136a 152 156a-2 154 156a-1 26. 121c 129b 131b-1 133 136b 156b-1 43a 46 46b 27. 121d 123 124 125 126 127 128 129 133 136a 136b 139a 139b 148 149 28. 38-b 29. 131a 156a 38a 38b 30. 146 150 151 153 155a 1a 2 3 38a 38b 4 43a 43b 5 6 31. 38b1 38b2 38b3 38b4 38b5 38b6 32. 121d 129b 131a 131b 133 136b 156a 156b 37a 37b 37c 33. 38a 38b 153a 129b 136b 155a 150a 43a 84a 159a 43b 34. 136b 150b 153b 155b 159b 84b 35. 158 160a 160b 162 38a 38b 43a 43b 36. 121c 47c-1, 121d, 1, 2, 3, 4, 5

DETAILED DESCRIPTION

The Protective American football helmet depicted in the accompanying graphics is representative of all protective helmet types. The overall structural design objective for this new technology, as an apparatus, is that of its design to protect the central nervous system: head, neck, and, indirectly, even the torso relevant to the tandem relation between the torso and the head being positively subjective to the tandem bracing relationship of the neck as described herein. It is designed for protections against impacts to the head/neck while the wearer is on his/her feet or upon falling to the ground—It is not for the head alone but inclusive of the head and torso. Pages 1-3 are representational only; they grossly depict the inter-correlations among the component elements as referenced so as to present the overall unique structural design concepts for the objective operations of the novel technology.

Page 1

FIG. 1 Ref. 10 is the space taken by the padding and cushioning of typical football helmets. This space around the head is central to the application of the novel technology, Impact Flexi-Brace product herein presented. The total cushioning area 10 is the integral “safety zone” for the wearer's head which is traditionally relied upon by manufacturers of such helmets. A helmet not featuring the novel bracing technology, as seen here in FIG. 1 would sustain injury 18 since 16 is the maximum movement environment for the head at time of any exterior impact from any direction; it is the Safety (virtual protective) Zone of Integrated Head and Neck Tandem-Bracing Device outside of which impact injury may be presumed—as in this illustration. Reference 12: is a measured deviation (space) from which an exterior impact would cause a jolt to a wearer's scull within his protective helmet. 14 a shows the neck sustaining serious trauma at instant of exterior impact as head itself is forced against inside wall of protective helmet. The cushioning is condensed by the depression causing the impact to have an equally damaging effect due to hitting a hard material. 16 Safety Zone of IHNTBD (above impact is injurious since it is outside of this Safety Zone, 16). The point of cranial impact 18 for sustained injury do to impact against compressed, hardened, padding as would be the case with conventional protective helmets. Ref. 12 further shows (expanded/magnified view) concentric 360° boundary segments around the head for split-second “bracing” points at which the pneumatic compression retraction process would cause the helmet to lock in-place for as long as external impinging pressure is held. 20: head, cranium of wearer, 22: protective helmet.

Page 2

Turning to FIG. 2, Ref. No. 12 shows theoretical boundary segments for split-second “bracing” points within which the mechanism would cause the helmet, (and the entire protective apparatus—head, neck. & torso) to lock in-place for length of time any of the pneumatic impact tube components remain compressed from moment of an exterior impact. They are possible “freeze points” for a given impact at which moment helmet would brace against any movement: Ref. 16 thus would entail boundary 12 illustrations 1-6, further causing the helmet, (and the entire protective device—head, neck. & torso) to lock in-place for length of time any of the corresponding pneumatic impact component processes remaining compressed against the helmet, (or other protected segment) from moment of an exterior impact. It is to be noted also that the neck reference 14 b should be compared between those of FIG. 1 Ref. 14 a and FIG. 3 Ref. 14 c for effect of an impact; head 20 and the helmet 22. 16: is a virtual boundary (safety zone) within which is the containment as shown in FIG. 1. It is a virtual comfort zone provided by IHNTBD within which zone there would be no injury to wearer's neck at moment of an exterior impact. The mechanism for independent movement of head with helmet for the independent movement effect of 16 is a segment of the harnessing device (partially shown here) 24 which is part of harnessing apparatus securing the protective helmet, and other facilities, to the head of a wearer. Columnar Support/Positioning Component 26 is beneath Impact Damping/Suppression Cradle 28. The bracing event may initiate upon off-center movement of 26 with respect to 28 which is contiguous to it. For Insertion/Locking Element for executing impact movements with respect to the Impact Damping/Suppression Cradle, see FIG. 30 Refs. 26 and 106. The representative reinforcement stabilizing device 30 is the central tandem clinching and bracing structural factor of the invention. 31 is a representational anchoring structure for the associated components: 36, 35 a, and 41 a of FIG. 4A.

Page 3

In FIG. 3 Ref. 14 c, it should be noted that the neck, as indicated, is only slightly bent; this is due to the small degree, if any, of movement of the head toward the right, consequent to an exterior impact event; as so, the force of impact, in this case would be negligible against any injury. Accordingly, this is a scenario showing how the novel product arrests any contact of the wearer's head with the interior surface of a protective helmet upon sustaining an impact. Compare the appearance of the neck here with that of FIG. 1 wherein the head is not protected by the bracing device. The proposed standard protective device for the head is evident in FIG. 2 and its positive performance effect in FIG. 3.

FIG. 3 No. 32 Shows maximum movement of head before bracing. It does not go outside this safety zone; also, there is only a minimal disturbance of the neck 14 c not in danger of any injury. The impacting element may be from any angle around the helmet; the result will be similar—not proceeding to the extent as shown in previous illustration FIG. 1 where the head may reach maximum suppression of the cushioning/padding and thus increased likelihood of trauma to the head, in addition to the neck and torso, by association. Shown above, impact angle 32 is the maximum limit, (at any impact point/angle, 360°) to which the player's head can move within area 12 the confines of the soft cushioning sector—area 12: virtual boundary space within which the mechanism would cause the helmet, (and the entire protective apparatus—head, neck, & torso) to lock in-place for length of time any of the pneumatic impact tube components remain compressed from moment of an exterior impact. 10: the space taken by the padding and cushioning of typical American football and hockey helmets; 14 c: illustration of minimal bending of the neck after an impacting jolt. 26: Support Column and Insertion/Locking Element for attenuating impact jolt movements with respect to the Lateral Movement/Flex Mechanism Component. In this illustration, a lateral impact movement is presumed based upon off-center of column; see FIG. 26 Ref. 106. The distance is somewhat exaggerated. The star reference 32 shows wearer's head impinging the, but there is no injurious impact, as the head had not been struck by the helmet wall. Ref. 32 indicates maximum leeway of movement prior to pneumatic bracing event; there is no injurious impact against inner wall of helmet! Accordingly, the excesses for “added” cushioning material would not be necessary in the space taken by the padding and cushioning of typical football helmets 10; further, the profound difference is the stopping power indicated by the bracing event. Compare the point-of-impact illustration of Page 1 FIG. 10 and this illustration; the profound difference is the stopping power indicated by the bracing event and as demonstrated by the basketball & bowling ball illustrations. Ref. 26 shows off-center displacement with respect to IDSC force of impact thus presuming its simultaneous correspondence with pneumatic compression processes, indicating both a damping of movement and, with other pneumatic compression processes a bracing event of entire apparatus, head, (helmet) neck, and torso. Again, FIG. 16 is the virtual, but physically holding and containment border within the helmet, being the maximum degree from central displacement of the head—the 360° Safety Zone barrier at onset of bracing. It is “comfort zone” provided by IHNTBD within which injury to wearer's neck would be mitigated. 28: Impact Damping/Suppression Cradle, 30: representative tandem stabilizing device; see Pgs. 11-15

Page 4

FIG. 4A is the frontal perspective of the Integrated Head and Neck Tandem-Bracing Device for protective helmets, and its anchoring components of the Collar-Shoulder Bracing Segment, 36, 41 a, 35 a, and FIG. 33 no. 35, showing the clenching/bracing device units around the neck. Upon a bracing event, each unit will effectively brace, or lock, movement of the corresponding components of the Integrated Head and Neck Tandem-Bracing Device, the helmet 45 and the anchoring components Collar-Shoulder Bracing Segment 35 a and the shoulder protection component 36, not allowing any movement of the head in either direction; this is due to the actions of the tandem friction/anchoring rod neck-stabilizing elements 39. It comprises also the Shoulder Protection Component 36 the shoulder protection area, also beneath which lies (at posterior) the Shoulder Impact Retraction Device. A Protective Helmet Clamp 37 is one of optional elements for securing the Harnessing apparatus FIG. 2 Ref. 24 to the helmet. Shown in 39, 44, and 46 a are partial views of the Integrated Head and Neck Tandem-Bracing Device units. Several of the opposing and coordinating friction stabilizing rods of the tandem friction/anchoring rod neck-stabilizing elements 39 are shown here; the retraction cord/wire 44 is the necessary element for effectively clenching its respective neck stabilizing unit module; they are the retraction cord/wires which connect/interact with tubular pneumatic compression unit in the helmet and other pneumatic processes for retraction in the apparatus; see FIGS. 5A-44, 7A, 7B, and 9A. Ref. 46 a is the covering for one of the, at least three, neck stabilizing unit modules. The Collar-torso Harnessing/Bracing Attachment 35 a is functional as an anchoring facility which is functional as an anchoring facility with the Collar Support Segment 41 a. Shown here also is an example of a protective helmet, the depiction of a typical helmet as worn in the sport of American football 45; it is a representative protective helmet, (generic illustration representative of any type of protective helmet: bicycle, bull riding, etc.) FIG. 4A, as the Integrated Head and Neck Tandem-Bracing Device for Protective Helmets, inhibits head concussion impacts. The framework herein illustrates an overall tandem relationship for head, neck, and shoulder areas of the wearer. The device operates together with the Collar-Shoulder Bracing Segment 35 and the shoulder protection area 36. The frontal, anterior, perspective of the apparatus shows the position of the Wire/Cord Retraction Module 46 (which is the enclosed aspect of the impact retraction/bracing unit); shown is the protective covering for one of the, at least three, tandem neck stabilizing units, (anterior view) indicating its design to retract a wire/cord element at integral positions around the shoulder/collar area of the Collar-Shoulder Bracing Segment 35.

Page 5

FIG. 4B is a partial posterior perspective of the Integrated Head and Neck Tandem-Bracing Device with its upper torso harnessing component, an exemplary protective helmet, and a segment of the pneumatic compression/retraction apparatus FIG. 24E-1 but not showing either anterior nor posterior Impact Shields and other bracing structures for now; FIG. 24E-1: a Pneumatic Compression facility beneath rear impact protective shield, (See Page 26) in place as it would appear as one of the several retraction components; FIG. 24E-2 is the Lateral (Shoulder) Impact Retraction Device, with Pneumatic Compression facility, nearing a retraction/bracing mode as can be seen by the position of the cylinder and piston configurations 471 and 47 h-4 after an impact as noted at 47L; FIG. 24E-2: is an enhanced depiction of the of FIG. 24E-1 so as to expand and exhibit the necessary identity reference numbers for the structural elements of the shoulder impact retraction/bracing device. This bracing component is ancillary to the primary pneumatic compression systems of the head, neck, and torso but for impacts against shoulders, (still, all four methods coordinate) further comprising the numbered reference 47 a, 121 d, 121 e, and those below: 47 b, c-1, c-2, d, e, f-1, g, h-1, h-2, h-3 i, j-1, j-2, 47 k, 47L, and continued FIG. 24E-2-47 f-2 on Page 36; 35 b: Collar-torso Harnessing/Bracing Attachment; 39 b: Opposing and Coordinating tandem friction/anchoring rod neck-stabilizing elements of two of the Tandem Neck Stabilizing Modules, (right side view); 41 b: Collar-Shoulder Bracing Segment; 46 b: protective covering for one of the Master Retraction Units of Tandem Neck-Spanning Stabilizing/Bracing Device, (posterior view); 47 a: element for shoulder/neck bracing; this is an element for initiating thoracic pneumatic compression component; it is designed to be pushed laterally inward from either an upright (standing) impact, or from a fall to the ground. This element No. 47 a has its duplicate on n opposite shoulder; 47 b: Conduction tube for conduction of rigid retraction control Rod 121 e which may both pushed downward by a pneumatic retraction response from helmet FIG. 8A and pushed for down stroke by shoulder retraction/pneumatic system, or pulled down by pneumatic retraction response from torso pneumatic compression process,

Thoracic Truss Compression Component FIG. 25A and FIG. 25B; see Rom. Num IV Page 28. 47 b allows passage of spindle-like rigid rod—not transference of compressed air as from above “closed compression chamber in the 47 c-1 environment. 47 c-1: Compression environment of the 3^(rd) pneumatic progression component, the Shoulder/upper-torso Retraction Device. This environment encompasses the area above piston 47 f-1. An active piston 47 f which causes two valves 47 j-2 and 47 k to alternate based upon which shoulder is being subject to an impact; they (valves) may operate simultaneously in the event that both shoulders are being impacted, whether by lateral hits or by other forms of physical tackle on a field of play. 47 d: This is a return spring—the process whereby the force of an impinging impact has been released; subsequently, this spring would naturally return for required reset mode. 47 e: both 47 e and 47 f are activated for pneumatic compression and downward pulling the retraction wire/cord element downward causing Master Retraction Unit FIG. 24D Page 14 to brace along with left and right retraction units FIGS. 24B and 24C to also brace. Interior of Pneumatic Compression Cylinder 47 e which facilitates initiation of a retraction process as caused by an impact to the shoulder, component 47 i is the paired element for accomplishing the same effect; piston 47 f, further, is subject to both pull down from rigid rod compression rod 121 e below and from rigid rod above consequent to a push down as caused by impact against the helmet; 47 f-1: piston component of the closed system compression cylinder 47 c-1; 47 g: This is the lower end of the compression/retraction pneumatic device; it is a funnel-like element for the free egress and ingress of air flow into, and out of, the lower chamber, allowing for the movement of the piston; the free flow of air is apparent by the apertures designed into the funnel-like element; accordingly, compression is not created in this area 47C-2 but in 47C-1; 47 h-1: area of concentration for piston process location as opposed to piston process location of Ref. 47 h-4, which shows process beyond air flow apertures 47 h-3 indicating that compression has occurred due to an impact as arising from any one of three locations, other than at its own location 47 h-1; 47 h-1 indicates the piston is in the pre-compression, rest, position.

47 h-1 and 47-h 2 are compared based upon pneumatic valves 47 j-2 and 47 k, whether a valve is open as in 47 j-1, indicating influx of air and that piston 47 f-1 is being drawn downward for either helmet impact (from above) or for impact at torso Impact Shield retraction component. Either one of the three processes would draw air into the chamber 47 c-1 above the piston 47 f-1, opening both valves 47 j-2 and 47 k as in 47 j-1. Alternatively, upon one of the shoulders receiving an impacting jolt, the opposing valve would close. This may be seen somewhat with the impacting event as indicated by the right shoulder in the drawings of both FIG. 24E-1 and FIG. 24E-2. More clearly, in 24E-2, an impact is sustained as referenced by 47L. The primary piston rod 471 has been executed (pushed inward) causing secondary piston/rod to telescope laterally outward, tensing a return spring 47 d, opening the corresponding valve 47 k, (See 47 j-1) forcing valve 47 j-2 to close (not allowing egress of air through opposite side) thus causing compressed air in 47C-1 which forces the piston downward, pulling with it the spindle rod 121 c above it, in effect, causing clinching and bracing event for the tandem neck-spanning device while, at same instance, (with spindle down stroke) causing the frictional facility FIG. 35C-1 a of FIG. 35C-2 and the fixing of the prong protrusion FIG. 35C-3 to coordinate (pierce for fixed mobility) with rear side of impact shield FIG. 35A-38 b while between anterior side of Thoracic Truss Compression Component 133 of FIG. 25A which has an outer anterior friction surface designed for slide stoppage against the side of Compression Impact Shield Fastener FIG. 35C-3 which also has a friction surface on one side, in addition to having projecting prongs for attenuated, fixed, movement on the opposite side. The overall object of this process is tandem bracing between head, neck, and torso but, further, for independent bracing against both injury to the torso and to whiplash. Such protection is specific for 360° due to the wearer's immediate “braced fortification” of the neck on the one hand, and for assurance against lateral impacting jolts from any angle—and without the wearer having to initiate the device; it is mechanically automatic. The force of such jolt is divided against the mass weight of the wearer's entire body, instead of just the mass weight of the head alone. If, as opposed to a single—side impact against just one shoulder, as above, both shoulders are impacted about the same time, both valves 47 j-2 and 47 k would be necessarily thrown open, both piston locations as 47 h-4, will also have been pushed past the air aperture openings thus circumventing creation of an immobilizing vacuum for movement of the pistons; 47 h-3: apertures (air ingress) allow transit of piston from its normal, at rest, non-compression, position as at 47 h-1 and 47 h-2. Again, the main piston 47 f-1 will still carry out the three major pneumatic compression benefits described above. This device FIG. 24E-1/24E-2 is designed to protect against three vital vulnerabilities: 1. Tandem bracing between head and torso; 2. Direct circumvention of whiplash as the body is braced, 3. overall protection of central nervous system CNS. These, in addition to the other impact suppression measures of the apparatus, are the multiple protective management objectives of the Integrated Head and Neck Tandem-Bracing Device in safeguarding the natural neurological processes of the central nervous system CNS. Erroneously designing new technologies for the helmet shells for the head alone will still earmark the neck for taking the G-force impact collisions. This is a fatal mistake causing short-term and long-term medical and neurological health maladies. The neck has to manage each and every hit sustained by the head. The more comprehensive and intelligent standard is to intelligently engage the entire body in the protective process by simply securing the neck, and so the head, against involvement in brutal impacting collisions; this is possible; it is bio-mechanically sound, even scientific.

Page 6

FIG. 20 shows a Friction Anchoring Rod 50 as it would appear within a Friction Rod Jacket/Sheath 62, in open position; the same is seen at FIG. 21 but in closed position with the Contraction Cord 87/88 tightly withdrawn; the friction contraction cord pulls together the contraction studs 98 of FIGS. 22 and 23. In FIG. 21 Friction Rod 50 and Jacket/Sheath 62 are in closed aspect; further, both are of a high friction material for excellent slide/stoppage capability at instance of clinching for a bracing event. FIG. 22 indicates the retraction structure at rest, as in FIG. 20 with Friction Rod Jacket/Sheath open, (not engaged for bracing) thus allowing freedom of friction rod movement, with the contraction studs 98 apart from each other. FIGS. 22 & 23 Ref. 98 are Contraction Studs. FIG. 23 Ref. 100 is a Retaining Guide for channeling friction contraction cord 87/88 for the coming together of the two Contraction Studs 98. Ref. 102 is the point towards which contraction studs 98 move for tightening of Contraction Wire/Cord 87/88. A contraction wire retainer guide 101 separates and stabilizes the related, but independent, processes of each retraction pair set. FIG. 21 No. 63 is the tightened, retracted, mode of the retraction wire/cord element necessary for closed aspect of Friction Rod Jacket/Sheath 62.

Page 7

FIGS. 10a-10c -1 and 10 d-10 f illustrate several structural positional mode aspects taken by the stabilizing retraction/bracing friction rod units as coordinated with the natural movement positions of the wearer's head/helmet; FIG. 11 shows an approximate perspective view of a scaled-down depiction of how the tandem neck-spanning device would appear with the three clinching/bracing units. These are Friction/Stabilizing Rod configurations. All illustrations entered here are positions taken by the rear retraction set; the same or other variations may be taken by the other Friction/Stabilizing Rod unit modules. They all illustrate several of the positional aspects taken of the Friction Anchoring Rod Sets for the neck stabilizing modules as observed from the rear of a protective helmet; these are based upon the corresponding positions taken by the natural movements of the user's neck with respect to the head. FIG. 10a : indicates the head is bowed forward, FIG. 10b : indicates that the head has turned to the right, FIG. 10c -1: indicates that the head is turned upwards, FIG. 10d : indicates that the head is turned upwards and to the right. FIG. 10e : indicates that the head is turned upwards and to the left, FIG. 10f : indicates that the head is turned more extremely forwards than illustration in FIG. 10a ; Ref. 10 c-2 of FIG. 11 is presented here only for the purposes of example of how the three clinching/bracing units are structurally arranged around a wearer's neck; this referenced item would actually be the Master Retraction Unit, (which it is not) as it would be located at the back of the neck in this depiction:

Page 8

FIG. 16 is a partial view of one of the Friction Anchoring Rod Sets; partial depictions of the friction retraction wire/chords 87 and 88 are shown, detailed previously on Page 6. FIG. 17 indicates partial structural configuration showing how the wire/cords would be retracted and released as connected to friction rod jacket/sheaths Nos. 62 a, and 62 b; a Fixed Pivot Bell Crank 70 is for use as a lever mechanism with respect to retraction wire/cords 44 and bracing friction rods 50. Opposing Friction Rod Jacket/Sheaths 62 a and 62 b, Fixed Pivot Bell Crank arm 70, and a Return Spring 68, operate in correspondence with lifting of arm of FPBC 70 in a retraction event consequent to an exterior impact. FIG. 18 partially shows one of, at least three, side retraction units in non-clenched, non-bracing, mode of the neck stabilizing; 104 a is the wound retraction wire/cord element in un-contracted mode, signifying non-contraction of retraction unit FIG. 19 shows one of, at least three, side retraction units in clenched, bracing, mode of the Integrated Head and Neck Tandem-Bracing Device; 104 b is the wound retraction wire/cord element in contracted mode signifying retraction of retraction units; it is the tightened, retracted, wire/cord necessary for closed aspect of Friction Rod Jacket/Sheath, thus initiating a clinching aspect for facilitating a bracing event consequent to an impacting exterior jolt to the protective apparatus.

Page 9

FIG. 5 illustrates a partial structural view of one of the Integrated Head and Neck Tandem-Bracing Device retraction/bracing units, including its Foundational Anchoring Support 64 and Module Cushioning Support 58 which also facilitates extended head movements; these constitute additional means of cushioning against, particularly, vertical bottom-up and vertical top-down impacts. Ref. 42 represents the external housing of a protective helmet. The retraction wire/cord element 44 when retracted pulls upward causing friction sheaths 62 a/62 b of FIG. 17 Page 8 to close with subsequent retraction. Ref. 46 a/b is a protective covering for one of the Tandem Neck Stabilizing Units. Refs. 48 and 50 are opposing Coordinating Friction/Stabilizing Rods, which are essentially the tandem and stabilizing elements required for the bracing event. A spring action is internal to this element 72. Receptor for Suspension Rod 74 allows multi-directional flexible movement. Fastening bolt 78 is for friction connection for rod movements. An internal spring-like element, flexion anchoring support (downward shock-suppression) 80 provides additional shock absorbent benefit.

Page 10

FIG. 6 is an exploded view of the one of the neck stabilizing modules. Shown herein are the retraction wire/cord element 44, the Collar Shoulder Bracing Segment 41, Friction Bracing Rods 48/50, opposing peripheral module cushioning hinge-rod supports 58/60, anchoring supports 64 which also provide within their structures a spring-like cushioning element; Rotary Hinges for Friction Bracing Rod Jackets 66, Return Springs 68, and Fixed Pivot Bell Crank 70 for leverage manipulations of 66 and 62 for accomplishing the bracing objective of the Friction Bracing Rods 48/50. Also, Fixed Pivot Bell Crank 70 is for use as a lever mechanism and for opposing and coordinating structural functions; see Page 11 FIG. 7A, FIG. 7B. Return Springs 68 are necessary for resetting the clinching process after a retraction/bracing event.

Page 11

FIGS. 7A and 7B are interior representations of the Wire/Cord Retraction Modules of the neck spanning/stabilizing safety device; Collar-Shoulder Bracing Segment 41, Return Spring 68 necessary for resetting the retraction elements subsequent to a clinching/bracing event. The environment for essential point for retraction interactions among the Opposing, Coordinating, Friction Bracing Rods and friction jackets 52; also see FIGS. 18 and 19, in addition to FIGS. 24B, 24C, and 24D P. 13 for facilitating the clinching/bracing process; the depiction. FIG. 23, Page 13 shows structural unique structural characteristics of the rear module not utilized by the two side bracing modules FIGS. 22A and 22B. An Interior Housing Section 82 of the protective helmet allows substantial fixing of elements such as the return spring 68; and partial depiction of the retraction/friction rod assembly 52; the interior attachment component 82 is grossly minimized in dimension and shape for purposes of illustration. In FIG. 7B the retraction wire/cord element 44 is shown, as it would appear, between interior protective plate 46 and exterior protective façade, 42. Ref. 46 is further detailed as an interior bracing protective abutment which is continuous around the wearer's head, within the helmet, to the opposite side, (from edge of face guard opening to edge of face guard opening) structurally serving as a hedge between the retraction modules and the wearer's head. It is a pillow-like, fibrous, closed, air-filled chamber, from end to end around the wearer's head. The Foundational Anchoring/Suspension Support 64 is more fully detailed and explained on pages 9 and 10 and elsewhere in the drawings.

Page 12

FIGS. 9A and 9B represent views of the Wire/Cord Retraction Modules as they would appear grouped within a protective helmet. One is interior 9A; the other is exterior 9B. FIG. 9A shows a interior area of the protective helmet showing the three grouped Wire/Cord Retraction Modules of the neck spanning/stabilizing safety device. Ref. 44 is the retraction wire/cord element for the purpose of coordinating clinching among the three retraction units in the process of bracing; for further observation of process, see FIG. 24 Ref. 44 and FIGS. 8A, 8B. An outer protective covering FIG. 9B-42 is shown, (and as would be seen by a casual observer) with an optional decorative surface/veneer 86; the covering 42 would be an industrial-strength, heavy duty protective mechanism, capable of withstanding the intense rigors of field sports such as American football, hockey, and others; accordingly, the bracing friction rods as would be seen in illustrations FIGS. 10-15 of page 7, pages 13, 14, 16, and illustrations elsewhere would not be readily seen by players on the field of sports, further preventing players from intentionally, or unintentionally, getting their fingers into an opponent's protective helmet for gripping purposes.

These elements would, necessarily, be constructed of a rigid but somewhat minimally flexible material for the natural neck and head movements of the wearer. Collar-Support Bracing/Anchoring Segment 41 is indicated as the segment which serves as initial foundational support and anchoring member; it is connected to the Collar-torso Harnessing/Bracing Attachment FIG. 4A-35 a of page 4. 121 d: Wire/Cord which facilitates “pull” for downward process of exterior impact clinching event of Master Unit

Page 13

FIGS. 24B, 24C, and 24D are the two secondary retraction units and the primary Master Retraction Unit, respectively; they further describe: 44: retraction cord/wires; 50: Friction/Stabilizing Rod; 62 a: Friction Jacket in open position; 68 a: a return spring in the non-flexed mode; 82: An Interior Housing Section of the protective helmet allows substantial fixing of elements (such as the return spring 68) for stability; FIG. 24C: 50: Friction/Stabilizing Rod; 62 b: Friction Jacket 62 b is closed around Friction/Stabilizing Rod; 68 b: return spring shown here in the flexed mode indicating retraction and so bracing of the module; 96: the Rivet/bolt Hole at the base of the Friction/Stabilizing Rod allowing the Friction/Stabilizing Rod to be fixed and allowed to move; FIG. 24D: The Master Retraction Unit: (conduit for subordinate retraction units); 68 c: return spring shown here in the non-flexed mode indicating non-retraction and non-bracing of the module; 69: shadow representation of one of the Opposing. Coordinating. Friction Bracing Rods; 70: Fixed Pivot Bell Crank is for use as a lever mechanism and for bracing Opposing, Coordinating, Friction Bracing Rods Ref. 50; 100: Retaining Guide for channeling friction contraction wire/cord; 101: contraction wire/cord retainer guide separates and stabilizes each retraction set; 104 a: wound retraction wire/cord element in un-contracted mode, signifying non-contraction of retraction unit; 121 b: Rigid Connecting Rod-2 which facilitates push/pull downward process for clinching of Master Impact Retraction/Bracing Unit; 121 c: Rigid Connecting Rod-3 which facilitates push/pull downward process for clinching of Master Impact Retraction/Bracing Unit; FIG. 24B indicates the retraction structure at rest, in non-bracing mode, with Friction Jacket open 62 a around the Friction Anchoring Rod 50 shown singular here. In FIG. 24C, Friction Jacket 62 b is closed around Friction Anchoring Rod, singular rod shown here. Ref 68 a of FIG. 24B is a return spring in the non-flexed mode. It acts to return the Fixed Pivot Bell Crank FIG. 24D No. 70 (and Ref. 70 of FIGS. 17 & 18 etc.) back to its non-bracing/non-retracting mode. FIG. 24C indicates an engaged bracing stage depiction of FIG. 24B indicating the retraction structure in its retraction/bracing mode, the return spring shown here 68 b in the flexed mode. FIG. 24D specifies the rear retraction module as the singular and exclusive component of the retraction modules which will feature a revised configuration of the Fixed Pivot Bell Crank depicted here labeled A and B as well as a structural variation for the procedure for a bracing event as explained for FIG. 24D page 14. The lever system is used for initiating a bracing event originating both from either the protective helmet pneumatic component, or one, or both, of the torso pneumatic components, (right-side, left-side, peripheral, and anterior/posterior impact shields) sections each of which would initiate a conjoined bracing event, that is consequent to an impact to the protective helmet or to any part of the torso, each corresponding for mutual protection from impacting events. This technology provides still additional protections against falls to the ground, irrespective of manner: back-first, left/right shoulder-first, head first, etc. The retraction cord/wires 44 for bracing are exclusive for helmet impact; spindle-rod 121 a is specific for rear module as initiated by torso pneumatic impact components. No. 96 is the rivet hole at the base of the friction rod.

Page 14

The is the overall structural and operational appearance of the Impact/Retraction Structure and the Primary Pneumatic Compression Device, further indicating the three inter-coordinated clinching/retraction units. FIG. 24A is the Primary Pneumatic Compression Device; 44: retraction wire/cord element for retraction module facilitating left and right retraction unit/modules; see fuller (complement of) structural components for retraction and pneumatic retraction processes on Page 28; 49: left guide tube for Wire/Cord 44; 51: guide for downward push of rigid push rod 121 a; 53: Tubular Pneumatic Compression Device: primary compression chamber; 54: right guide tube for Wire/Cord 44; 55: telescoping (secondary compression) chamber enclosure section of Tubular Pneumatic Compression Device; 56: exterior push/pull housing for Rigid Connecting Rod-1; 57 a: secondary compression chamber of the Tubular Pneumatic Compression Device showing smaller space indicating non-compression, at this point 59 a: primary pivot node allows necessary turning movements; 61: Inner Sheath separating harness and secondary impact cushioning 65; 65: Secondary Impact Cushioning Elements; 67: outer lining separating the primary impact cushioning and secondary impact cushioning 65; 73: area to be occupied by the head harnessing component and the Impact Damping/Suppression Cradle; 121 a: Rigid Connecting Rod-1 which facilitates push/pull downward process for clinching of Master Unit; 121 b: Rigid Connecting Rod-2 which facilitates push/pull downward process for clinching of Master Unit; FIG. 24B: Left Impact Retraction/Bracing Unit; FIG. 24C: Right Impact Retraction/Bracing Unit; FIG. 24D: Master Impact Retraction/Bracing Unit—serves to retract wire/cord elements of left and right Impact Bracing Units in addition to the shoulder impact retraction event by being subject to a “pull down” retraction process with consequent clinching and bracing of each unit, left, right, and itself as master control unit. (See FIG. 8A and FIG. 8B Page 15 for retraction process of the Master Impact Retraction/Bracing Unit/Module; note: “unit” depicted un-chambered, “module” when in covered, chambered, protective covering); 68 c: return spring shown here in the non-flexed mode indicating non-retraction and non-bracing of the module; 69: outline depiction representation of one of the Friction/Stabilizing Rod elements; 70: Fixed Pivot Bell Crank is for use as a lever mechanism and for bracing Opposing. Coordinating, Friction Bracing Rods Ref. 50; 100: Retaining Guide for channeling friction contraction cord; 101: contraction wire/cord retainer guide separates and stabilizes each retraction set; 104 a: wound retraction wire/cord element in un-contracted mode, signifying non-contraction of retraction unit; 121 c: semi-rigid, wire/cord, which facilitates downward pull process of Lateral (Shoulder) Impact Retraction Device, (Page 5 FIG. 4B1-47 a-f) for clinching of Master Retraction Unit; 121 d: Wire/Cord which facilitates “pull” for downward process of exterior impact clinching event of Master Unit; FIG. 24A depicts the Primary Pneumatic Compression Component and is the neck spanning/stabilizing device, which, together with the Torso Impact Compression Component. Pages 27 and 25-35 constitute the essential protective structure of the Integrated Head and Neck Tandem-Bracing Device.

Page 15

FIG. 8A: Master Impact Retraction/Bracing Unit in the un-contracted, non-bracing, mode; 44: retraction wire/cord element for retraction module facilitating left and right retraction unit/modules; 51: guide for downward push of rigid push rod 121 a; 56 a: exterior push/pull chamber for push rod; 57 a: secondary compression chamber of the Tubular Pneumatic Compression Device showing smaller space indicating non-compression; 59 a: primary pivot node; 59 b: secondary pivot node; 71 a: arrow showing compression status as neutral, non-compressed; FIG. 8b : Master Impact Retraction/Bracing Unit in the contracted, bracing, mode; 56 b: exterior push/pull chamber for push rod—indicating compression sequence: forward advance of push rod for retraction; 57 b: secondary compression chamber of the Tubular Pneumatic Compression Device showing larger space indicating compression for consequent retraction of Master Impact Retraction/Bracing Unit which causes right and left retraction units also to retract; 71 b: Arrow shows compression status as compressed; Master Impact Retraction/Bracing Unit is in the contracted, bracing, mode; 121 a: Rigid Connecting Rod-1 which facilitates push/pull downward process for clinching of Master Unit; 121 b: Rigid Connecting Rod-2 which facilitates push/pull downward process for clinching of Master Unit;

Page 16

FIG. 32A, FIG. 32B, FIG. 32C, FIG. 32D are the harness securitization clamping and impact compression elements; FIG. 32A shows the overall appearance of the un-manipulated element; 75 a: Lead Arm rotates outward (1. contracts 2. expands out (for both attachment to tube and for impact event)) in process for compression of Tubular Pneumatic Compression Device consequent to an exterior impact; 76: head of tube containment/constricting element; 77: rotational rivet for movement of lead arm; 79: Tandem Sync Arm (moves in coordination with Lead Arm for); 81: rotational rivet for movement of Base Arm; 83 a: Base Arm functions to compress pneumatic tube when impacts are vertical; FIG. 32B specifies an element being modified based upon a directional impact impingement; 83 b: Base Arm facilitates compression from vertical, either impact down or impact up; see FIGS. 37C & D P. 17; FIG. 32C shows an example of one of the elements being impacted from the left having the effect of compressing the pneumatic tube which would be in the clinching area of this element; 75 b: Lead Arm turned inwards due to side impact with consequent compression from Lead Arm; FIG. 32D indicates one of the functions of the design of the elements; it can be seen here in the open, receptive, mode for either its removal from, or connecting to, the compression tube; this is also the position it would take for compression of the tube at moment of an impact from opposite side of a protective helmet; 53: shows tube end of the principal element comprising the pneumatic compression device; 85: showing Lead Arm and corresponding Tandem Sync Arm 79 in position for either securing tube to helmet or being forced outward due to impact to helmet; 89: These arrows show process of the tube containment/constricting element in the mode for being connected to, or being disconnected from, a compression tube; also, this is the structural mode for compression of the pneumatic tube at moment of an impact.

Page 17

FIGS. 26A, 26B, 26C, and 26D further display details of the modifications of the harness securitization clamping and impact compression elements: 75 b: Lead Arm is pushed inward at moment of external impact, compressing pneumatic tube unit; FIG. 26B, 91 a: Lead Arm is thrust outward due to lateral impact from opposite side of helmet, pulling Tandem Sync Arm outward causing compression of compression tube; 91 b: Tandem Sync Arm (Page 16 FIG. 32A Ref. 79 moves in coordination with Lead Arm for impact effect); FIG. 26C, 93 a: Head of tube containment/constricting element is pressed downward, from coronal impact to helmet, forcing impingement at bottom, Base Arm 94 a, of tube containment/constricting element, thereby causing compression of pneumatic tube unit; 94 a: Base Arm facilitates vertical compression due to either downward and/or upward; FIG. 26D, 93 b: Head of tube containment/constricting element is subject to upward thrust from bottom with Base Arm 94 b facilitating compression of pneumatic tube unit; 94 b: Base Arm is functional in vertical compression—upward or downward;

Page 18

FIG. 28A: tube containment/constricting element in place prior to constriction/compression of the primary compression chamber of the Tubular Pneumatic Compression Device; FIG. 28B: Head of tube containment/constricting element is pressed downward, from coronal impact to helmet, forcing impingement at bottom of tube containment/constricting element causing compression of primary pneumatic compression tube unit; FIG. 28C-1: Rotational Impact—left pushes head of tube containment/constricting element in such manner as to cause directional constriction/compression causing retraction/bracing; FIG. 28D-1: Rotational Impact—right pushes head of tube containment/constricting element in such manner as to cause directional constriction/compression causing retraction/bracing; FIG. 28C-2: Rotational Impact—left, as seen from above segment in FIG. 38C-1; FIG. 28D-2: Rotational Impact—right, as seen from above segment in FIG. 38D-1;

Page 19

FIG. 29A: This is a top-down perspective view of the tubular pneumatic compression unit, an interposed compression sheath, one of, and, at least, eight tube containment-constricting element; 95: tube containment/constricting element and its constriction/compression ring, (showing one of, at least eight) in place prior to constriction/compression of the primary compression chamber of the Tubular Pneumatic Compression Device; 96: top-down view of rear, Master Impact Retraction/Bracing Unit; 53: primary compression chamber of the Tubular Pneumatic Compression Device; FIG. 29B: top-down view of the secondary Impact Retraction/Bracing Unit; 61: Inner Sheath separating harness and secondary impact cushioning 65; 65: Secondary Impact Compression Cushioning—compression is internal and local to the element; 67: outer lining separating the primary impact cushioning and secondary impact cushioning 65; FIG. 29C: Impact Damping/Suppression Cradle showing slight damping from an impacting jolt; 97 a: Impact Damping/Suppression Cradle centering node visually indicates degree to which IDSC has been deflected off center due to a jolting impact to the helmet, shown here by slight deflection; 138: The central Column Cap beneath, and contiguous to which is the Impact Damping/Suppression Cradle and the cranial harnessing component; FIG. 29D: Impact Damping/Suppression Cradle showing secondary slight damping from an impacting jolt; 97 b: Impact Damping/Suppression Cradle Centering Node indicating an impact jolt slightly more than that of 97 a FIG. 29C; 99: transient bar along which Circular Flex Rings expand outward and inward due to a more than average force impact 103: A section showing a further outward crest indicating off-center positioning of 97 b, still such jolt may not be cause for injury; FIG. 29C and FIG. 29D reflect the movements made by consequent jolting action as received from impacting forces exterior to the protective helmet, so they depict another, added, layer of impact protection beyond the pneumatic compression process. No. 138 the covering for the columnar apex movement position of FIG. 30 Ref. 26 for damping of peripheral movement of the head harnessing apparatus against both direct impacts to the protective helmet and right-angle shoulder impacts with the ground due to falls; see FIG. 30 Nos. 106 and 122. FIG. 29-D illustrates the extreme extent to which Central Column Cap thus the harnessing element may go if the impact is severe enough. The Impact Damping/Suppression Cradle FIG. 29-C and FIG. 29-D are designed to suppress-by-reflex any jolting movement, (displacement from central position) of the Impact Damping/Suppression Cradle No. 28 FIG. 30 by increasing degree from the slightest to the more resistant based upon the jolt of an exterior impact. For example, columnar apex movement position of FIG. 30 Ref. 26 from that of FIG. 29-C to that of FIG. 29-D has more resistance in FIG. 29-D at near maximum position at edge of the IDSC Impact Damping/Suppression Cradle farthest position from center of the IDSC. Such process occurs as the “primary” and “independent” jolt from a fall to the ground “without” retraction action of Friction Anchoring Rods of the Neck stabilizing unit Modules. However, it is the “secondary,” but “coordinated,” (with friction anchoring rod modules) process upon sustaining an impacting peripheral jolt against helmet due to both upright impact, such as in American football, and a fall to the ground.

Page 20

FIG. 12A: 28: perspective view of the outer rim of the Impact Damping/Suppression Cradle; FIG. 12B: This is a side perspective view of the Impact Damping/Suppression Cradle; 34: underside of Impact Damping/Suppression Cradle wherein is the upper surface/top of the Harnessing Apparatus.

Page 21

FIG. 27A-1: This is a top-down perspective view of the tubular pneumatic compression unit, outer rim representation of a protective helmet, an interposed compression sheath, at least eight tube containment-constricting elements, and Impact Damping/Suppression Cradle; 95: tube containment/constricting element and its constriction/compression ring; 99: transient bar along which Flexible Impact Suppression Rings expand outward and inward due to a more than average force impact; 130: top-down cutaway view of the rim of a protective helmet shell; 134: Flexible Impact-jolt Suppression Ring; 142 a: view showing one of the tube containment/constricting elements, the small distance between the protective helmet and the tubular pneumatic compression unit, and the separation sheath between helmet rim and the tubular pneumatic compression unit; FIG. 27A-2; 103: compression tube surface rim consisting of a malleable durable material; 104 a: interior of compression tube indicating an empty environment except for air; FIG. 27A-3: 53: side view of compression tube; 104 b: side/end view of opening of the compression tube;

Page 22

FIG. 27B: This is a top-down, cutaway, perspective view of the tubular pneumatic compression unit, outer rim representation of a protective helmet, several tube containment-constricting elements affixed to the tubular pneumatic compression unit, Secondary Impact Cushioning Elements, and the Impact Damping/Suppression Cradle—not showing the interposed sheaths as in depiction of Page 21 FIG. 27A; 107: one of the containment-constricting elements indicating increased distance between the helmet rim and the TPCU due to an exterior impact on the opposite side of TPCU: in the case of this depiction, the forward five of eight such elements will indicate an outward push of helmet rim and its own compression effect; 108: one of the containment-constricting elements indicating increased distance between the helmet rim and the TPCU due to an exterior impact on the opposite side of TPCU; in the case of this depiction, the forward five of eight such elements will indicate an outward push of helmet rim and its own compression effect; 134: Flexible Impact-jolt Suppression Ring; 142 b: depiction here shows closed space due to helmet impact in contra-distinction to reference 142 a FIG. 27A of Page 21; FIG. 27C: depiction of the effects of an impact to one side of a protective helmet with respect to opposite side of same helmet, FIG. 27D; 53: Tubular Pneumatic Compression Device: comprising the primary compression chamber; 75 b: Lead Arm of one of the tube containment/constricting elements is pushed inward at moment of external impact, compressing pneumatic tube unit; 109: side of protective helmet receiving an exterior impact, transmitting force of impact to opposite side; 111: shows the compressed structure of the tubular pneumatic compression unit consequent to impact on the impact side of the protective helmet and the working of one of the tube containment/constricting elements 75 b; FIG. 27D: depiction of the effects of an impact to one side of a protective helmet FIG. 27C with respect to opposite side of same helmet. FIG. 27D; 91 a: Lead Arm is thrust, pulled, outward due to lateral impact from opposite side of helmet, pulling Tandem Sync Arm outward causing compression of tubular pneumatic compression unit; 91 b: Tandem Sync Arm (Page 16 FIG. 32A Ref. 79 (moves in coordination with Lead Arm for impact effect); 91 c: shows compressed structure of the tubular pneumatic compression unit consequent to impact on the opposite impact side FIG. 27C No. 75 b of the protective helmet and the working of one of the tube containment/constricting elements 91 b.

Page 23

FIG. 30: 24: part of harnessing apparatus which secures the protective helmet, and other facilities, to the head; 26: Support Column and Insertion/Locking Element for executing measured impact movements with respect to the Impact Damping/Suppression Cradle; see FIG. 26 Ref. 106; 28: Impact Damping/Suppression Cradle; 35: Collar-Torso Harnessing/Bracing Attachment; 41: Collar-Torso Harnessing/Bracing Attachment; 44 a,b: Retraction wire/cords for retraction units (Left and Right) FIG. B and FIG. C, respectively; 53: primary compression chamber of the Tubular Pneumatic Compression Device; 65: Secondary Impact Cushioning Elements; 68: Retraction Return Spring in non-retraction mode; 105: wire/cord conduction tube leading from 118 b and right retraction unit to 118 a and Master Retraction Unit; 106: Insertion/Locking Receptacle for Support Column and Insertion/Locking Element 26 which itself is attached to the Impact Damping/Suppression Cradle FIG. 25a No. 28; 108: upper components, (helmet attachment ends) of pneumatic tube containment/constricting elements; 110: support platform for primary compression chamber of the Tubular Pneumatic Compression Device; 114: the Vertical (top-down Impact) Depression Cushioning component; 116 a: inner crown of harnessing apparatus which secures the protective helmet, and other facilities, to the head; 116 b: head band segment of the harnessing apparatus which secures the protective helmet, and other facilities, to the head; 117 a: in-place element of FIG. 38A Page 18; 117 b: in-place element of FIG. 38B Page 18; 118 a: confluence area for compressed air and retraction wire/cord element processes; 118 b: hinge cover for wire/cord conduction; 120 a: Master (Rear) Retraction Unit; 120 b: Left Retraction Unit; 120 c: Right Retraction Unit; 121 b: Rigid Connecting Rod-2 which facilitates push/pull downward process for clinching of Master Unit; 121 c: non-rigid, wire/cord, which facilitates downward pull process of Lateral (Shoulder) Impact Retraction Device, (Page 5 FIG. 4B1-47 a-f) for clinching of Master Retraction Unit; 122: the generalized area for the retraction/bracing process; FIG. 30 is the representative and generalized protective helmet structural frame component of the neck spanning/stabilizing safety device with its cranial harnessing component. 68: shows a return-Spring Mechanism for each of the two, (left and right) Friction Anchoring Rod Sets for the neck stabilizing modules; a Columnar Support Column 26 for an Insertion/Locking Element Component 106 firmly connects harnessing component to the protective helmet; 35: Collar-Shoulder Bracing Segment—106: Insertion/Locking Element for 126 which itself is attached to the protective helmet; it can be dislodged using release implement at interior central apex area of the harness. 108 Multiple, at least A, B, C, and D (“D” not shown): are Bracing Activation Spindles which respond to both vertical impact depression as well as upward push of protective helmet. These spindles comprise the bracing elements for up and down helmet movements as well as for the alternative triggering mode of bracing involving a vise-like operation against the retraction cords within the Impact Bracing Band 116-B which responds to peripheral external impacts. 112: One of at least four detachment latches for the Vertical Impact Depression Cushioning—used for detaching the cushioning from the harness. 114 is the Vertical (top-down Impact) Depression Cushioning. 116-A (FIG. 2 Ref. 24 Harnessing apparatus) is the Interior crown surface of Harnessing apparatus. 116-B (FIG. 2 Ref. 24 Harnessing apparatus) is the Impact Bracing Band which responds to peripheral external impacts. 116C- (FIG. 2 Ref. 24 Harnessing apparatus) is the Head Band Segment of Harnessing apparatus. Ref. 118 is one of three representative Structural Lead Points between the Impact Bracing Band 116-B and one of the Wire/Cord Retraction Modules 120 a. 118 a, (for rear module) is one of the protective housings within which are the retraction cord/wire connection points for both 47, (unseen here—See FIG. 31E) and 121 a, in addition to the wire/cord Routing Device 132 and 132′ of FIGS. 31E and 31F; ref. 47 shows the dual-wire retraction scheme; 121 a is within the protective housing 118 a.

The modules 120 a, (rear) 120 b, (left side) and 120 c, (right side) of helmet are shown here with generalized, non-functional depictions of their Friction/Anchoring Rods and each of their clinching mechanisms of Neck stabilizing module (See FIGS. 20 through 25). 121 a is a descending retraction wire/cord member for pneumatic retraction activation: See Page 29 FIG. 36, 121 a and FIG. 37A. 121 b & 121 c are front and rear descending Stabilization Retraction wire/cords. 28: (FIG. 2 Ref. 28 Impact Damping/Suppression Cradle): Outer Boundary of Impact Damping/Suppression Cradle; see FIG. 28. Within this outer boundary, there is structured a cranial impact telemetry monitor which transmits and/or stores impact data as received from within the IDSC. The essential purpose of the device is to provide spring-like cushioning for horizontal and vertical movement of the protective helmet as sustained by an external impact to the helmet. The central Column Cap 138 FIG. 27A is the connecting component for which the cranial harnessing component FIG. 26 is held, contiguous to the protective helmet. Movements made independently by the helmet, or independently by the cranial harnessing component, are reflected by measured displacements of the Central Column Cap 138 FIG. 27A. This Central Column Cap is connected as an element of 26, 106, and 126.

A Helmet Bracing Path Ring 124 initiates immediate bracing process at moment of impact as facilitated by several Bracing Activation Spindles 108-A, B, C, D, etc. spaced around a Helmet Impact Bracing Band 124, and contiguous to it. Once either depressed or thrust upward, (as corresponding to movements of protective helmet) at any location around the helmet, bracing process is initiated. Accordingly, such Helmet Impact Bracing Band 124 is sensitive to relevant movements to the helmet due to falls and impacting jolts, including those that are rotational and deflectional to the helmet; see FIGS. 31A, 31B, 31C and 31D. An IDSC Impact Damping/Suppression Cradle Recess 106 is for insertion of Insertion/Locking Element 26 which locks Helmet harnessing apparatus into place until dislodged by latching element at base of Support Column and HHSCR 110. Such locking of HHD into place does not prevent its flexible movement within frame of Impact Damping/Suppression Cradle 28; see FIGS. 29-A, B, and C. A Helmet Harnessing Securitization Clamp Receptacle 110, (one on both side of the Head Harness Device) receives the Latching Mechanism 145 FIG. 32 of the Helmet-to-Harness Securitization Clamps: open 144 and closed 146 of FIG. 32. The HHSCR 110 is secured to Helmet Impact Bracing Band 124, not to a segment of Head Harness Device 24 FIG. 2 thus not impeding peripheral, vertical, or rotational movements of the protective helmet shell/structure 147 FIG. 32 “away from” Head Harnessing apparatus, (a triggering process) at instant of an impacting jolt, as is appropriate and necessary for initiation of a bracing event. Accordingly, the novel technology inhibits peripheral, vertical, diagonal, and rotational impact jolts to the head of the wearer to a greater degree than all relative safety equipment available since they do not provide a secure neck stabilizing unit as a bracing structure spanning the neck thus locking the tandem movement between head and torso at moment of exterior impact to the helmet or due to a fall. The graphic representations for FIG. 26 are generalized and does not show strapping such as a chin strap.

Page 24 FIG. 31A

28: Impact Damping/Suppression Cradle; 85: structural mode showing Lead Arm and corresponding Tandem Sync Arm 79 (page 17) in position for either securing tube to helmet or being forced outward due to impact to helmet; 90: depiction of Lead Arm in place within containment slot which would pull arm outward due to lateral impact from opposite side of helmet, pulling Tandem Sync Arm outward causing compression of pneumatic tube; 95: tube containment/constricting element and its constriction/compression ring, (showing one of, at least eight) in place prior to constriction/compression of the primary compression chamber of the Tubular Pneumatic Compression Device—same as in FIG. 38A Page 18; 104 a: interior of compression tube indicating an empty environment except for air; 113: interior Helmet Attachment Plate for connecting tube containment/constricting element, thereby connecting both the harnessing apparatus, in turn securing the protective helmet, and other facilities, to the head; FIG. 31B: 34: underside of Impact Damping/Suppression Cradle wherein is the upper surface/top of the Harnessing Apparatus; 65: Secondary Impact Cushioning Elements; 67: outer lining separating the primary impact cushioning and secondary impact cushioning 65; 106: Insertion/Locking Receptacle for Support Column and Insertion/Locking Element No. 26 age 23 which itself is attached to the Impact Damping/Suppression Cradle FIG. 25a No. 28 Page 20; 110: Support Platform for the corresponding elements of the helmet; 125: Adjustment Groove for optional position placement of Helmet Attachment Plate—amenable to various insertions of exchangeable technologies.

Page 25

FIG. 33 depicts the front exterior suit of protective gear as would be seen by wearer but without the traditional team brand over-garment of typical shirt and trousers. Each suit of protective gear would be tailored to the specific player, but with respective characteristic differences among the sports of hockey, American football, etc. In addition to the fundamental introduction of this protective gear in FIG. 4A, ancillary tiers of protective components are presented herein following: Front Position Impact Brace Shield FIG. 35B-1-38 a; it is designed as malleable sufficiently enough for natural synchronous body movements of the wearer; however, it necessarily has limited movements only at moments of impact bracing events. This shield FIG. 35B-1-38 a, as is the posterior shield identical to it, is partially anchored to Front Positional Stability Rods 156 a-1 156 a-2, 156 b-1, 156 b-2, in addition to other contiguous elements of the apparatus, particularly at moments of bracing events in which such elements would hold the Impact Positional Brace Shields FIG. 35B-1-38 a and FIG. 35B-2-38 in place as the rods 156 a-1 156 a-2, 156 b-1, 156 b-2 are anchored for support by both the Stability Anchoring Belt 154 and Thigh Support 152 elements for anchoring thus providing added strength and integrity to the Collar-Shoulder Bracing Segment 35 a, 36, and 41 a being fixed at the neck for tandem bracing and so further providing protection against whiplash shock, in addition to other injuries; this protective shield FIG. 35B-1-38 a is just one of the several pneumatic compression and other structural protective components. The foregoing protections are, otherwise, structurally engaged upon initiation of an impact, then engaging safety functions as indicated on Page 32 FIG. 39B for inhibiting impact movements which may cause whiplash. Thigh Supports 152 do not brace with any bracing event of the protective gear, they are simply an additional means of substantial protective support against vertical downward thrusts; such actions would be sustained by the neck spanning/stabilizing safety device as as per design of the tandem protective apparatus. Further, the Supports 152 would function, with the Positional Stability Rods 156 a-1 and 156 a-2 in preventing ease of movement at moments of clinch-bracing.

They provide stabilizing support for FIG. 35C-3 against rear of Impact Shield against possible whiplash. The Supports 152 are held securely in place by their component connection with the Stability Anchoring Belt 154 and, at least, a Velcro product strapping, fastening buckle 139 a and 139 b of FIGS. 25A and 25B. Impact Brace Shield may be initiated by FIG. 35B-1-38 a, at any point around the torso, including the shoulder impact device FIG. 24E-1 or FIG. E-2 Page 5 by impact or otherwise; such depression would be cause for retraction initiation of rear assembly of retraction module. 44: Retraction Cord/Wire necessary for facilitating compression/retraction sequence for clinching/bracing; 45: American football helmet used for reference purposes to indicate all protective helmet types; 46: protective covering for one of the three tandem neck stabilizing modules; 131 a-1: right side front of compression conduction tube which carries compressed air from FIG. 25A FIG. 35C-3 to 129 a at moment of clinch-bracing; 131 a-2: Left side front of compression conduction tube which carries compressed air from FIG. 35C-3 to 129 a at moment of clinch-bracing; 131 a-1; 129 a: compression transfluence distributor (right side) for receiving compressed air flows from both 131 a-1 and 136 a then redirecting them to rear FIG. 35C-3 for clinch-bracing; 136 a: right side conduction tube leading from Thoracic Truss Compression Component; 136 b: left side conduction tube leading from Thoracic Truss Compression Component; FIG. 25A and FIG. 25B: Thoracic Truss Compression Component; 39: tandem friction/anchoring rod neck-stabilizing elements.

Page 26

FIG. 34 is a rear view of FIG. 33 Page 25 depicting the corresponding components herein. The equipment constitutes the suit of protective gear as would be used by the wearer but without the traditional team brand over-garment of typical shirt and trousers. Each suit of protective gear would be tailored to the specific player, but with respective characteristic differences among the sports of hockey, American football, etc. Refs. 37B, 46 b, and 156 b are rear aspects of the same items as identified on the front and rear aspects of the same protective gear as seen in FIGS. 4A, 4B, and 33. In addition to the fundamental introduction of this protective gear in FIG. 4B, a second tier of protective components are presented herein; FIG. 35B-1-43 a: exterior side of posterior impact shield; 46: protective covering for one of the three tandem neck stabilizing modules; 121C: rigid connecting Rod-3 of Master Impact Retraction/Bracing Unit; 129 b: opposite to 129 a page 25; 131 b-1: left side rear of compression conduction tube which carries compressed air from FIG. 35C-3 and 129 b at moment of clinch-bracing; 131 a-2: left side compression conduction tube which carries compressed air from FIG. 35C-3 to 129 a at moment of clinch-bracing; 133: Thoracic Truss Compression Component; 136 a: right side Conduction Tube leading from Thoracic Truss Compression Component FIG. 25A/FIG. 25B; 136 b: left side Conduction Tube leading from Thoracic Truss Compression Component FIG. 25A/FIG. 25B; 131 b-2: right side rear of compression conduction tube which carries compressed air from FIG. 35C-3 and 129 a at moment of clinch-bracing; Posterior Positional Stability Rods 156 b-1 and 156 b-2 prevent ease of movement at moments of clinch-bracing. They provide stabilizing support for FIG. 35C-3 against possible whiplash.

Page 27

FIG. 25A shown here is the outer exterior side of the exterior of the Thoracic Truss Compression Component; its surface layer 133 is of frictional material for purpose of impeding sliding motion between itself and friction side/surface of CISF FIG. 35C3 and whose opposite side projects a prong set piercing the impacting impact shield either FIG. 35B-2-38 b or FIG. 35B-2-43 b Page 35 thus (being pressed against each other during bracing) preventing overall turning or torque action of the wearer's torso, thereby likely preventing dangerous whiplash; accordingly, 3600 lateral impact protection is afforded the wearer of the Integrated Head and Neck Tandem-Bracing Device; 121 d: Wire/Cord which facilitates “pull” for downward process of exterior impact clinching event of Master Unit; 133: friction surface layer of Thoracic Truss Compression Component facilitates pneumatic compression FIG. 25A/FIG. 25B which, when contiguous with FIG. 35C-3, one of whose surfaces also is of a friction material, operates to immobilize any sliding movement between the two, TTCC FIG. 25A/FIG. 25B and CISF, Compression Impact Shield Fastener FIG. 35C-3 at moment of impact clinching/bracing; 139 b: left side buckle/attachment for Thoracic Truss Compression Component; FIG. 25B shows the interior side of the Thoracic Truss Compression Component; 123: compression feed tube; 124: Thoracic Compression Chamber for tributary conduction feed to 128 for distribution to 136 a and 136 b; 126: return spring for piston 127 at moment of release of compression; this action also refills the upper impact compression units 148; 127: pneumatic piston fro pull-down process for connecting rod-4 121 d for executing tandem bracing event; 128: an air compression distributor divides oncoming compressed air between conduction tubes 136 a and 136 b; 136 a: right side Conduction Tube leading from Thoracic Truss Compression Component FIG. 25A/FIG. 25B; 136 b: left side Conduction Tube leading from Thoracic Truss Compression Component FIG. 25A/FIG. 25B; 139 a: right side buckle/attachment for Thoracic Truss Compression Component; 139 b: left side buckle/attachment for Thoracic Truss Compression Component; 148: upper impact compression unit facilitates action for downward pull of piston 127 only; 149: lower impact compression unit; FIG. 25C depicts an end of a Thoracic Truss Compression Component FIG. 25A and FIG. 25B; 125: exterior border of Thoracic Truss Compression Component; 129: air compression funnel conduit transfers air from lower impact compression units 149 then to conduction tubes 136 a and 136 b, which carries it to CISF FIG. 35C-3 for bracing of torso pneumatic component. Such air is returned to the units 149 for subsequent impact event; 136 a: right side Conduction Tube leading from Thoracic Truss Compression Component FIG. 25A/FIG. 25B; 149: lower impact compression unit.

Page 28

FIG. 8A, FIG. 24D, FIG. 24E, FIG. 25B, and Ref. 38 b are scaled-down interior aspect of overall structural depictions of the arrangement of the four coordinated retraction and pneumatic compression components of the apparatus as would be worn by a user; Roman numeral Tiers one and two are located within the rear of helmet; Roman numerals three and four are exterior to, and below, the helmet; FIG. 35A-38 b shows interior side of the Thoracic Truss Compression Component, TTCC FIG. 25B; between these is the Compression Impact Shield Fastener. CISF FIG. 35C-3.

Page 29

FIG. 35A shows two depictions of the torso impact shield: anterior and posterior; 38 a: front side of Impact Shield; 38 b: rear side of Impact Shield; 131 a: anterior right side of Compression Conduction Tube; 156 a: anterior right side of Positional Stability Rod; 35C-2: Compression Impact Shield Fastener, which upon moment of clinch-bracing, adheres to outer surface of TTCC FIG. 25B and, due to its prong projection feature, becomes “fixed” for the bracing moment with rear surface of Impact Shield. Both CISF and TTCC mutually hinder movement due to their contiguous friction surfaces sliding against each other at moment of bracing; FIG. 35C-4: anterior side of Compression Impact Shield Fastener FIG. 35C-2, which, upon impact, at opposite side of Impact Shield FIG. 35A-38 a, projects its prongs and adheres for frictional sliding against anterior surface 133 of Thoracic Truss Compression Component FIG. 25A/FIG. 25B.

Page 30

FIG. 35C-2 is a side view of the CISF; FIG. 35C-3 depicts the projected fastening prongs of CISF; such prongs pierce a wide area of the opposite sides of both anterior and posterior Impact Shields as shown in FIG. 35B-2. FIG. 35B-1 and FIG. 35B-2 represent the front and rear Impact Shields, respectively, as they would be worn over the torso of the wearer; FIG. 35A-38 b and FIG. 35C-3 show how the rear side of an Impact Shield and a Compression Impact Shield Fastener CISF FIG. 35C-3 would interface for coordinated fixation of movement at moment of bracing. The opposite side of this element CISF comprises a friction layer which slides interacts with anterior side of TTCC FIG. 25B, which itself has a frictional surface 133 so as to impede any movement at time of bracing; FIG. 35C-la depicts a side perspective view of CISF showing the friction material surface required for a stopping power at moments of clinching and bracing; on one side of the CISF element are the projected prongs that are pushed by force of an impact into the rear surface of the impact shield; FIG. 35C-4 indicates the prong-projected mode of CISF as seen in its environment FIG. 35A Page 29; FIG. 35C-1 b indicates the backing of CISF FIG. 35C-5 which also shows an approximate interior structural view of CISF in its un-projected phase; FIG. 35C-6 is an approximate exploded interior view of functional elements of CISF, in its un-projected phase; its components comprise: outer layer of frictional material 146; activation spring 150, representative of all springs in the unit, which facilitates projection and retraction of prongs, control member 151 which balances the movement of the prong and compression elements, prong element 153 which projects forward into rear of an Impact Shield, and compression tube 155 a which transfers compressed air to opposite side compression tube for the purposes of frictional stoppage and projection of prong element; see FIG. 40A and FIG. 40B page 34.

Page 31

FIG. 35A-38 b 1 through FIG. 35A-38-b 6 depict a variety of positional bracing positions as fixed by the Compression Impact Shield Fastener FIG. 35C-3 corresponding to the various fixing, bracing positional aspects as determined by the incidental Impact-bracing events with respect to the wearer's body positions; CISF FIG. 35C-3 here indicates wearer's torso has been fixed to an extreme right side of Impact Shield at moment of impact; accordingly, prongs are projected into rear side of shield and opposite side, friction surface, of this element adheres to friction surface of TTCC FIG. 25B.

Page 32

FIG. 39A and FIGS. 39B-1, 39B-2, and 39B-3 indicate the structural sequences and correspondences among the three independent pneumatic compression processes utilized for bracing events against impacts thus making this new technology quite unique as a viable deterrent against head, neck, and torso injuries on the field—not focusing on the head alone, a fatal error. FIG. 39A and FIG. 39B-1 depict the same impact and compression structure except FIG. 39B-1, FIG. 39B-2, FIG. 39B-3 (Anterior Side and Posterior Side) are in clinching mode 37 b, 37 c depicting the CISF prongs FIG. 35C-3 as engaged with the back side of an Impact Shield FIG. 35B-2, and opposite side of CISF facilitating frictional slide attenuation, being pressed against anterior side of Thoracic Truss Compression Component FIG. 25A for a bracing event; the rear side surface of this CISF features a surface frictional layer which facilitates stoppage of movement as it interacts with surface of the torso pneumatic compression component 133 of the TTCC FIG. 25A. FIG. 39A-37 a shows a CISF element prior to an impending impact. On both of its sides, it is plainly seen that its prongs are not projected on one side, and there is space on the opposite side between it and TTCC 133 indicating there is no attenuated frictional sliding; at moment of impact, CISF 37 b of same unit projects its prongs into rear of impact shield, and its frictional side meshes with frictional side of TTCC 133. This process is shown in FIGS. 39B-2 and FIG. 39B-3, the CISF element 37 c providing bracing of torso against torso injury and whiplash. 133: planar surface of the Thoracic Truss Compression Component FIG. 25A/FIG. 25B conveys compressed air to 131 a and 131 b; its surface is sheathed with layer of frictional material for inhibiting sliding at moment of clinching and bracing as component 35C-3 coordinates with TTCC's friction surface against its own friction surface; 121 d: Wire/Cord which facilitates “pull” for downward process of exterior impact clinching event of Master Unit; 131 a: anterior side compression conduction tube which carries compressed air to and from CIFSF FIG. 35C-3 and TTCC FIG. 25A through 129 a, 129 b, 136 a, and 136 b at moment of clinch-bracing; 131 b: rear side of compression conduction tube which carries compressed air to and from FIG. 35C-3 and 129 b at moment of clinch-bracing; Posterior Positional Stability Rods 156 a and 156 b prevent movement at moments of clinch-bracing. They provide stabilizing support for FIG. 35C-3, between Impact Shield FIG. 35A-38 b and Thoracic Truss Compression Component FIG. 25A and FIG. 25B, against trauma of torso and possible whiplash;

Page 33

FIG. 40A depicts the anterior and posterior shield surfaces with intervening Compression Impact Shield Fastener CISF FIG. 35C-3 device with its pneumatic compression transfer component in non-engaged, non-bracing mode; 38 a: front side of anterior Impact Shield; 38 b: rear side of anterior Impact Shield; 43 a: front side of posterior Impact Shield; 43 b: rear side of posterior Impact Shield; 84 a: un-expanded prongs of posterior Compression Impact Shield Fastener CISF FIG. 35C-3 prior to an impacting jolt; *129 b: same element on opposite right side (opposite) of torso; 136 b: conduction tube for conveyance of compressed pneumatic air from TTCC FIG. 25A/FIG. 25B; such flow of air co-mingles with flow from Pneumatic Impact Compression Vesicle 155 a; 150 a: a return spring, representing all such springs of unit, for resetting configuration of interior structures after an impact; see FIGS. 35C-5 and 35C-6 Page 30; 153 a: un-expanded prongs of anterior Compression Impact Shield Fastener CISF FIG. 35C-3 prior to an impacting jolt; 155 a: Pneumatic Impact Compression Vesicle, a bladder-like malleable pouch containing a specified amount of air, an impact to one of the Impact Shields causes the vesicle to empty its contents along conduction tubing to flow with effused air from conduction tubes 136 a/136 b of TTCC FIG. 25B at 129 a/129 b both are confluent expressly for activation effect at opposite side of apparatus for purpose of bracing; 159 a: a Pneumatic Impact Compression Vesicle in pre-inflation mode, as such Pneumatic Impact Compression Vesicle 155 a remains until moment of impact/bracing arising from alternate side of apparatus.

Page 34

FIG. 40B: is of the same subject matter as in FIG. 40A but indicating here the clinching aspect of the anterior and posterior Impact Shields, with relevant interior structural effects due to exterior impact; 84 b: expanded prongs of posterior Compression Impact Shield Fastener CISF FIG. 35C-3 after an impacting jolt; prongs penetrate the back side of Impact Shield and its opposite frictional side impinged against the frictional side of TTCC 133 for bracing thus facilitating protections against trauma to torso and whiplash of the neck; 136 b/136 a (& 131 a, 131 b of FIGS. 39B-2, 39B-3): receive influx of compressed air from impact side of apparatus; 150 b: a return spring, representing all such springs of unit, for resetting configuration of interior structures after an impact; in this case, after impact, the spring appears to be expanded, or tensed due to expanded effect of the Pneumatic Impact Compression Vesicle 159 b; 153 b: expanded prongs of anterior Compression Impact Shield Fastener CISF FIG. 35C-3 after an impacting jolt; impacting action causes both CISF components FIG. 35C-3 to become fixed for general bracing or torso and, through other processes, the tandem bracing of head and shoulders; 155 b: Pneumatic Impact Compression Vesicle here, after an impact, has been depleted 100% of its air contents which is transfused to opposite side of apparatus to alternate Pneumatic Impact Compression Vesicle at 159 b, which doubles in volume so as to project its prongs forward to the rear side of Impact Shield and for expansion to have CISF to push its other side against frictional surface of TTCC 133 which is not shown in these depictions of FIGS. 40A and 40B; 159 b: Pneumatic Impact Compression Vesicle is shown here as inflated due to transfusion of compressed air from opposite side of apparatus subsequent to an exterior impact.

Page 35

FIG. 35A shows the independent front side 38 a and back side 38 b of the Impact Shield; FIG. 35D shows an open configuration of the front and rear impact shields as connected; FIG. 35B-1-38 a is the anterior front side; FIG. 35B-1-43 a is the posterior front side; FIG. 35B-2-38 b is the anterior back side; and FIG. 35B-2-43 b is the posterior back side; FIG. 35D-158 shows a generalized aspect of how the apparatus may connect the front and rear shields over the shoulder of a wearer; 160 a shows a fastening implement for securing the apparatus; FIG. 35E is a closed side perspective view of FIG. 35D; FIGS. 35D and 35E represent the depictions of Page 30 FIG. 35B-1 and FIG. 35B-2; reference 160 b shows that the apparatus will have an appropriate securitizing method; reference 162 indicates the apparatus will be adjustable for size and build of the wearer.

Page 36

FIG. 24E-247 f-2 shows referenced subject matter from page five. Specifically, the pneumatic cylinder is grossly generalized here for purposes of detailing the working environment of the piston 47 f with respect to its capability of maintaining a closed system as it is pushed for the down stroke and its return. The structural features of the cylinder environment here FIG. 24E-2-47 f-2 references that of page five only to the extent of showing how the piston maintains a solid planar surface for an air tight chamber while it is at the top of the cylinder but rotates as it moves downward so as to open air flow apertures C-5 as it reaches the bottom of the cylinder; at this point, the apertures being open, the piston is easily returned to the top where it has again rotated to close the apertures for the closed environment necessary for the other processes, each of which operate cooperatively with the others with their individualized compression methods. Piston A should be understood to be at top of cylinder with closed apertures Ref. A-1; cylinder B indicates air is allowed to flow through the open apertures B-2 as designed; the cylinder chamber, itself C is designed with twisting, grooved, striations C-3 on its interior wall to facilitate rotational movement of the piston; a variety of appropriate guide elements C-4 may fit into the striations.

How it Works (A): Operational Processes Outline—

An exemplary football helmet will be used for illustration purposes in the following descriptions as a model for all relevant protective helmets though they differ in specific structural design.

-   -   The design of this new technology entails multiple protective         processes: Pneumatic Compression Retraction, Impact Attenuation,         Static Cushioning, Pneumatic Flow Transfer Chambers, Anchoring         Suspensions, front and rear Impact Shields, and a Thoracic Truss         Compression Component; a general outline as to how they operate         follows:         -   I. Inertial Mass Deflection of Impact—(pneumatic             compression/retraction):             -   1. Head: coronal, lateral, rotational, upward thrust,                 etc.             -   2. Torso (shoulder): lateral jolt, fall to the ground             -   3. Torso (front/rear): anterior and posterior shields                 against hazardous injuries: whiplash and other                 neurological hazards against the CNS.             -   4. Torso (left/right sides) compression unit during                 tackle         -   II. Ground Impact—(brace attenuation & pneumatic             compression/retraction):             -   1. Shoulder (right angle level to ground): neck (and                 head) are steadied on impact due to moment of rigid                 tandem bracing of the device between torso and helmet,                 protecting against neurological damage of cervix spine,                 (vertebrae of neck) and, secondarily, head trauma impact                 against the ground circumvented by the holding and                 attenuation facility of the IDSC.             -   2. Helmet (front/rear): Impact Damping/Suppression                 Cradle device serves to secure the head while                 suppressing and attenuating the jolt against both                 direct, forward and rearward, impact against surface of                 the ground; both IDSC and pneumatic compression arrests                 and cushions the head against the force of impact.         -   III. Process Methods for Pneumatic Bracing against Injurious             Impacts:             -   1. A substantial impacting object against protective                 helmet—(downward coronal, lateral, rotational, upward                 thrust, etc.) would initiate:                 -   a. IDSC for bracing and attenuation of impacting                     force.                 -   b. Pneumatic Compression Unit for retraction process                     of Master Retraction Unit with its two left and                     right side corresponding friction rod components for                     momentary clinching and bracing of neck, (head) as                     long as impinging force is held; this retraction                     process at the same time thrusts an actuation prod                     spindle to                 -   c. Static Cushioning Array, (Mini-Pillow Elements                     adjacent to PCU)                 -   d. Suspension Anchoring elements which absorb jolts                     exclusive to downward forces             -   2. A substantial lateral impacting object against a                 shoulder, (left or right) initiates three protective                 measures:                 -   a. Pneumatic retraction for downward pull of the                     activation rods initiating clinching action at                     tandem device for bracing of both helmet and torso                 -   b. attenuation of impact force             -   3. A substantial impacting object against Anterior                 Impact Shield             -   4. A substantial impacting object against Posterior                 Impact Shield             -   5. A substantial impacting object against left and/or                 right side of torso of the wearer: A depression against                 the Thoracic Truss Compression Component would                 independently initiate a pneumatic process for a                 “pull-down” (retraction) of Master Retraction Unit.

How it Works (B)—

Physical Law: INERTIA—Isaac Newton's First and Second Laws of Motion (summarized), friction, and pneumatic compression as related to the Integrated Head and Neck Tandem-Bracing Device.

-   -   1. First Law: “Forces that change an object's motion must first         overcome its (the object's) inertia.”     -   2. Second Law: “A force, acting on an object, produces an         acceleration which is equal to the force divided by the mass of         the object.”     -   3. Pneumatic Cylinder Compression:     -   4. Pneumatic Tubular Compression:     -   5. FRICTION: (Clinching/Bracing):     -   6. RETRACTION PROCESSES:     -   7. Deceleration of Impinging Forces by Fractional Distribution:         Transference of Mass Weight of a force exerted by an impacting         object to (across) tandem device:     -   8. Attenuation of Impacting Force:     -   9. Cushioning/Padding only at top of helmet for against crown of         helmet for downward force of impinging impact. Padding for sides         of helmet against lateral hits would introduce potential for         compressed, compacted, condition of such materials at moment of         an impact thus assuring . . . .

HOW IT WORKS (C)—The essence of the bracing moment against an impact specifies that the force of the impact simply had not occurred—or not as would be received without the provisions of the novel technology. At instance of an impact, the jolt is met with an opposite and equal force but equal as conditioned only by the prevailing mass weight difference of the heavier object after the division and equitable distribution of the mass weights between the two at moment of collision.

How it Works (D)—the “X-Factor” Stabilizing (Scaffold) Architecture

For both the tandem neck clinching device and the torso anterior and posterior impact shields, a solid foundation for anchored stability may be seen in the “X” structure that is also found in many modern buildings for stability. This feature may be seen in the depictions on pages 7, 25, 26, and 29. Accordingly, as mentioned in relevant parts of the specification, at moments of clinching/bracing, movement is impeded in all directions—based on this “scaffolding” attribute. The novel device incorporates this firm foundation for correspondence with principles of friction for retraction/clinching and pneumatic compression for the overall initiation of the bracing event at moment of an impinging exterior impact. Each of the two domains for bracing under this scaffolding scenario allow twists, turns, forward and backward, up, down, diagonal, etc. movements until precise moment of clinch-brace immobility. This moment being held until impinging impact is released if as in a pile-on or in a hold and take-down. Such clinch-brace may also be about 0.05 of a second or more in time.

The novel design herein offers a solution: Conventional protective helmet may be modified by subordinating the inner containment area to allow more space for measured “leeway of movement” of the inner wall as measured from the wearer's head since it is the helmet wall that “moves toward/against” the wearer's head. It is this impact movement, (of inner surface of helmet) that would be “arrested” in “split-second-time” by a bracing “intervention” of this novel system, locking it momentarily, with other segments of the apparatus receiving the force of such impact then distributing it to the mass “inertial weight” of the upper body of the wearer, “not, injuriously, to the head, or body, itself.” This “distributed” force had been divided by the mass of the “inertial weight” of the body since, the tandem bracing of the neck actually locks in the weight of the body as a counterweight for the interval that the compression/retraction is held. The remaining force is distributed about the apparatus—primarily the shoulders as the anchoring element, but further, the upper torso. Accordingly, this further lessens the jolt, protecting the torso, (spine) neck, and head—the three segments that are, literally, integral to the central nervous system. The helmet component will correspond “in-tandem” to the torso framework system by a collar-shoulder bracing segment, the essential technological device which is indispensable to this new invention for head and even torso protective gear. Helmet movements will correspond to the movements of the wearer's head precisely; helmet movements not consistent with willful movements of the head will cause a bracing event of both helmet and collar-shoulder bracing segment of device, with further activation of the torso component against whiplash.

The non-compacted, (non-cushioned) space, by design, inhibits an injurious impact since, a. onset speed of a mechanical clinching event will halt movement of helmet within a fraction of an inch, in time, as it braces itself; b. The modicum of cushioning material, more pliable than conventional padding needs, will be sufficient if there is any contact; and c., more pliable cushioning material proves more necessary at times when a player or wearer falls to the ground hitting his head, (within the helmet) against the cushioned lining of the helmet. In this latter event, the neck is not abruptly forced to bend downwards from the shock of impact, (itself often a traumatic event); it is supported, or “braced.” at the neck segment thus keeping the neck at pre-impact position and, so, preventing the helmet from striking the ground or, just as injurious, preventing adverse bending of the neck. Spinal cord injuries analyses, (so possible concussions) presume damage arising from area from the base of the spine to the neck and brain, so occasions for whiplash, adding to trauma to the head, neck, and torso are diminished. Further, necessary, (or intentional) field maneuvers such as spearing, can be cause for subluxation of the cervix spine.

The device, overall, may be thought of as an impact “exo-skeletal firewall” that, upon onset of an external impinging impact, to the helmet or shoulder, would immediately receive the kinetic mass weight of the impact and distribute it as divided by the “inertial mass” of the recipient object. Such recipient body, (inertial mass) receiving the “remaining” force of impact sustains it by distributing it throughout the apparatus the head would not sustain an injurious force of impact. If the head strikes the ground, a vehicle, or an opposing player on a field of play such as in hockey or American football, the head could be seriously shaken by sudden “deceleration.” This new technology would “attenuate” the sudden deceleration or the violent wobble of the brain within cranium; the deceleration would be more gradual than being abruptly stopped by the compacted and condensed cushioning as is currently the dilemma thus rendering such cushioning as a hard surface. This is secondary to the bracing component.

The protective helmet is secured to the head of the wearer in usual ways base upon the particular manufacturer and type of helmet. However, ample space should be provided for the head inside the helmet so as to allow impact movement of the inner wall of helmet prior to impact bracing before it touches the wearer's head. The triggering event is initiated by this “tandem-dependent” relationship. The free movement of the wearer's head would not trigger a locking event since such movement does not disrupt the tandem relationship.

Inertia—IHNTBD Reflects Physical Principles

The revolutionary idea, but straightforward, logical technology, entails a protective resistance mechanism against external impact injury; it is scientific, following Isaac Newton's First and Second Laws of Motion involving Inertia. With respect to this new apparatus, the effect/law is initiated at the precise moment of an external impinging object impact against the protective helmet or against the shoulder component of the device as it corresponds with the split-second timing of the pneumatic compression process involved in this new device. Impact Energy Dispersion exhibited in this novel technology is in line with the principles and laws of Inertia, demonstrating an act of dissipation at moment of collision and the release of energy.

The locking/bracing event of this new technology entails a parallel mechanism detailed above: Thus the “counter force” against exterior impact constitutes the inertial mass (weight) and/or the kinetic mass (weight while in motion) of apparatus wearer as engaged against an impinging mass weight of an exterior impact whose force would be distributed thus circumventing any injury to the head or torso; nor would the neck be adversely affected by either torque movements or bends, the neck, (collar-shoulder bracing segment) being the essential area for which the protective helmet bracing mechanism is engaged and upon which the invention is based.

The unique impact bracing apparatus hereby primarily protects head, neck, and torso of athletic sports tackle players in such field sports as primarily hockey and American football. It does not directly address involvement with the extremities of the human body, except incidentally, with respect to implications of neurological reach of the CNS. The IHNTBD seeks to protect the head, neck, and torso of the user. An alternative design, without the torso impact shield and torso compression components referred to above. IHNTBD would be more specific to activities such as lacrosse, rugby, bicycle riding, auto vehicle racing, rodeo bull riding, skateboarding, snowboarding, horseback riding, etc. This technology would be modified for competitions such as motorcycle, motor vehicle water course and motor vehicle road course car racing, in addition to other hazardous competitions.

Further Details as to the Working of this New Technology:

An external impact to the segmented apparatus, from any angle, will “brace/lock” all segments of the device, immediately engaging the (mass) weight of the wearer's upper torso, (by default of inertia) against such impact. By instantly locking upon impact, the apparatus aggregates to itself the total “inertial weight.” forming a unitary counter balance against the mass of the exterior impact—thus “softening the blow” from injurious hits. The vital parts of the body, head and neck primarily, of the wearer would be protected against the modicum of the force remaining, if any, since the total impact force has been divided by physical principles of inertia and kinetics and “distributed” at onset of impact thus causing such minimized force to be harmless—relative to its initial magnitude.

Re-emphasis is lain upon the significance of the error of conventional placement of padding in a protective helmet. It is too close to the player's head—all around. Compression of such padding thus caused by the impingement of the head against it initiates the onset of an impact; depending on the force of impact, it may contribute to the source of a concussion. The novel idea reverses the process somewhat. At moment of impact, the helmet is locked in place; accordingly, the force of impact would, now, have to overcome the inertial mass/weight of the torso, not just the head alone, due to the tandem bracing relationship. In this way, the exterior force of impact would then be “divided” against the inertial mass weight of the recipient of the impacting force, head, torso, and extremities thereby delimiting, or softening the overall impacting blow. The head does not travel to a mass of padding upon impact but is “arrested” in a fraction of a second by the bracing element then “flexioned” by the attenuating facility of the Impact Damping/Suppression Cradle progressively—from lighter to heavier resistance against movement of the head as physically determined by the weight of the player's head (counter weighted) against the player's own weight (of the torso). The impacting force would then engage the aggregated mass weight of the head and torso simultaneously. According to Physical law, for every action, there is an opposite and equal reaction.

Bio-Mechanical Observations

Vulnerability—The biomechanical relationship of the head and the torso with the neck in the middle is highly significant; at the instance of any incoming impact, the torso and head tend to part company—no matter the angle or measure of G-Force; whether the jolt is to the head or torso, at any speed, angle, or development of neck muscles of course, the link between the two is the neck, which responds to the slightest thrusting/jolting actions sustained by the head. The middle has to be immobilized at split second of an incoming jolt. An accordion can stretch outward and inward, in variable directions without damage to its middle, and compressed inward leaving both ends without damage; it is designed to do so. The cervix vertebrae have a central core as the one and only conduit, or thoroughfare, for countless neuronal transmissions and the vital CNS fluid, the cerebrospinal fluid, CSF. Additionally, the atlas and axis vertebrae do their jobs of upholding the head while allowing reasonable twists and turns; they comprise much of the management tools for a wide variety of movements. However, unwilling, unplanned, movements in the form of brutal downward, upward, and rotational, thrusts, lateral jolts, coronal depressions, violent thrusts to the ground, etc. may damage the control management mechanism for the head—the neck, which can further sustain permanent destruction of neural connections and upset the normal CNS functions. The human neck is not designed for sustaining multiple contortions, cervical/thoracic subluxations, etc. without eventual life altering damage which may lead to a multiple of adverse medical and neurological conditions, of known and unknown description as to cause stemming from neck damage. It requires optimal protection if health of a unified CNS is to be maintained. This optimal protection comes in the form of a bracing action, perfectly timed for encountering and arresting any offensively impacting jolts to the head, or to the body, by way of securitizing the neck from any movement caused by an external impinging impact against the “unified” apparatus—in the same rationale for maintaining the integrity of the CNS; it also is a unit but comprising brain and vertebral column between which vital correspondences must be maintained for overall health.

Concussion to the Spinal Cord—the Overlooked Result of Impact

Cervical Cord Neurapraxia CCN has been of particular concern among football players for over 25 years. It occurs from severe head collisions when a player's neck is either contorted in some way or bent far backward or forward with great force. Players in high-impact tackle interactions are most commonly affected. It further involves injury to the spinal cord that causes brief disturbance of sensation and/or the ability to move. Symptoms include numbness and tingling in the hands or feet as well as even brief complete paralysis. Areas of the body affected can be a single arm, a leg, or all four limbs. Effects can last less than 24 hours and often for just a few seconds, after which the individual may return to prior state before the injury. Spearing is an on-field maneuver which multiplies the incidences of this type of injury; it was banned from American football in the 1970's; still the problem remains due, in part, to the vulnerability of an unsecured neck at moment of an impact. The new technology herein seeks to address this problem introducing a new standard of safety through a new design for the overall protection of the central nervous system. The spine is referred to as “The pillar of Life.” The Atlas vertebra is at the top of the spine and is the most important link to the rest of the spine. The Atlas supports the skull; if it, and the Axis vertebra beneath it, malfunction, a wide range of musculoskeletal, circulatory, and neurological problems may arise. Even misalignment of the atlas can compress the nerves, arteries, and veins; so circulatory and neurological concerns may appear.

“Paradoxically, the modern helmet's superior protection of the head and brain promoted playing techniques that put the neck at risk for injury.”—Dr. Godon Bell, Dir., Center for Spine Health at Clevelend Clinic.

Alternative Embodiments

With the removal of the torso impact shields and compression impact components depicted in pages 25 and 26, and as further explained on pages 29 to 35, with appropriate modifications per activity and helmet type, IHNTBD would be applicable for athletic sports activities such as rugby lacrosse, and as well, a design, as modified for bicycle riders. Again, protective helmets for various other embodiments as mentioned in the specification are possible: all-terrain vehicles, motorcycling, horseback riding, rodeo bull riding, vehicle race course competitions, etc; accordingly, the scope of the invention should be determined not by the embodiment as illustrated herein as for hockey and American football but by the appended claims and their legal equivalents.

CONCLUSION, RAMIFICATIONS, AND SCOPE

Thus the reader will see that the Integrated Head and Neck Tandem-Bracing Device technology provides a highly reliable, and personally vital, protective equipment apparatus that can extend performance and endurance on the various athletic fields of sports but, more significantly, that it may help to preserve mental health and, even, life—for those engaged in the many field activities involving both head and torso impacts which are inevitable. While the description above contains many specifics, these should not be construed as limitations on the scope of the invention but, rather, as an exemplification of one preferred embodiment thereof. Other variations are possible. For example, modified application can be realized, (an alternative embodiment) with respect to the brutality of arena boxing; that is, this new product allows for a possible revolutionizing of that sport by making it a non-brutal, bloodless, event simply by employing the anchoring facility of the collar-shoulder bracing segment herein alone. Moreover, with respect to the stated collar-shoulder bracing segment, a protective unit, also exclusive of the torso, vest segment, and capable of independent effective operation as defined above, but only for bracing the neck and, thus, for protection against head impacts only, has its efficacy in guarding against head trauma, in addition to, by default, injury to the neck since all head impacts will affect the neck, it being the sole element of stability for the protective helmet—without the new technology being herein introduced.

This novel invention acknowledges and asserts that specified conventional body protective gear for a variety of sports activities such as hockey, American football, lacrosse, and rugby are inappropriate with respect to their designs to offset injurious impacts to the bodies of the players these sports activities. Their heavily-padded helmets, torso padding, etc. maintain various standards of protection against injury from impact during above-mentioned competitive events. However, such standards provide far fewer protections than those achieved by the new art herein presented. Those standards do not provide a protective body-bracing apparatus that sustains singular discrete-point impacts, as well as multiple event, consecutive, and simultaneous impacts, absorbing the force of such impacts, and distributing them throughout the apparatus while still circumventing injuries for the wearer of such protective apparatus as provided herein. This novel protective gear addresses primarily such athletic sports as hockey and American football but also to lacrosse, rugby, rodeo, bull riding, and others with relevant design modifications. Other subject-comparison protective gear types are relevant to hazardous occupational jobs such as industrial testing, etc. as well as to motorized vehicular water course and road course racing competitions as well as other competitive, but hazardous, sports arena events.

The Medical, Neurological, and Life-Saving Objective Benefits of the invention—In the consumer market for body protective gear in sports conventional personal body protective equipment is tied to a supposed effective level of protection against injuries. However, with the constant reports, now in the broadcast media in regards to athletic injuries, particularly in American football and hockey, it is now becoming apparent that the usual equipment has proven itself insufficient as a means of protection. The central nervous system extends from the brain and down through the spinal cord which is physically protected by the bony vertebral column. The functions of the brain and spinal cord facilitate as conduit for sensori-motor information. Upsetting this balance by physical impacts against both the head and torso can cause Traumatic Brain Injury since such impacts disrupt the delicate balance of the natural cushioning protections of the cerebrospinal fluid which encompasses the vital areas of the central nervous system, (in the brain and spinal cord): head, neck, and torso. IHNTBD seeks the greater standard in protecting the entire CNS from adverse assaults against head, neck, and torso. 

What is claimed is:
 1. A body impact bracing apparatus, comprising: (a) a vest/torso bracing framework component, including a torso jacket, a multiplicity of at least tubular bracing members together with their clench-switch devices, bracing modules WCRModule-1 and WCRModule-2 for correspondence of onset-of-impact bracing signals between said framework component, on one part, and a collar/shoulder bracing component, on the other, (b) the collar/shoulder bracing component for a protective helmet, including:
 1. a neck stabilizing and spanning device for said onset-of-impact bracing signals between the helmet and the vest/torso bracing framework component, said device consisting of at least friction and anchoring/controlling rods for means of immobilizing tandem movement between said protective helmet of the collar/shoulder bracing component and the vest/torso bracing framework component,
 2. a harnessing and position sensing device for detection of movements between the helmet and the vest/torso bracing framework component,
 3. a clamping device for securitization of said helmet onto the harnessing and position sensing device,
 4. multiple said clench-switch devices for said onset-of-impact bracing signals correspondence between said collar/shoulder bracing component and said vest/torso bracing framework component,
 5. a buttressing device for supporting the weight of said helmet on the head of a wearer of the apparatus,
 6. a lateral movement/flex damper device for damping any counter-movement of the head of the wearer against any side of interior wall surface of the protective helmet;
 7. at least one switching device for detecting multi-angular impressions, such device being contiguous with said damper device and said protective helmet; (c) at least one signal transmission means for correspondence of said onset-of-impact bracing signals for cessation of movement arising from one or more exterior impacts against said protective helmet, against the collar/shoulder bracing component, and against said vest/torso bracing framework component; (d) protective means for the head, neck and torso/spinal cord segments of the wearer of the apparatus, said segments being biologically predisposed as integrated and unified segments harboring the entirety of the central nervous system of the human body; accordingly, said collar/shoulder bracing component and said vest/torso bracing framework component of the apparatus are predisposed for inter-dependent bracing signals, and so constituting a mutually unified means of the apparatus for encompassing, thereby protecting, said integrated segments from injurious impacts, thus neither said collar/shoulder bracing component nor said vest/torso bracing framework component being exclusive to itself with respect to its own, independent, sending said onset-of-impact bracing signals or to its receipt of said signals; both said components interactively, and necessarily, correspond, providing means for mutual bracing protection as a dual-component unit, alternating said onset-of-impact bracing signals when required.
 2. The body impact bracing apparatus of claim 1 wherein said harnessing and position sensing device is concentrically disposed within said lateral movement/flex damper device which is functionally contiguous to the interior central crown area of the protective helmet.
 3. The body impact bracing apparatus of claim 1 wherein said vest/torso bracing framework component comprises a frame of at least a grating-like said array of a plurality of at least semi-rigid interconnection of at least tubular bracing members having means for facilitating intervals of bracing.
 4. The body impact bracing apparatus of claim 1 wherein said collar/shoulder bracing component is structurally attachable to, and contiguous with, said vest/torso bracing framework component for means of a coordinated bracing interval, said neck stabilizing and spanning device of the collar/shoulder bracing component, is functionally contiguous to, and disposed between, the base of said protective helmet along its lower edge and securely anchored and disposed within and about a shoulder guard harness of a wearer of the apparatus at the lower edge of the spanning device, said collar/shoulder bracing component being further securely anchored and buttressed around and about the waist of the wearer.
 5. The body impact bracing apparatus of claim 1 wherein said vest/torso bracing framework component comprises: a. electrical devices for contact between said exterior impacts and said clench-switch devices for inhibiting movement of at least tubular bracing members at multiple locations in said vest/torso bracing framework component, said electrical devices being channeled through bracing and cord retraction modules, said devices for said contact include at least: an actuator, signal transmission means, at least one electrical switch, a battery, electrical hard-wired conduction mechanisms capable of executing processes for effectuating said electrical devices for said contact and said bracing interval of the protective helmet, said collar/shoulder bracing component, and said vest/torso bracing framework component against said exterior impacts, b. mechanical devices for said contact is operative within said bracing and cord retraction modules of the WCRModule-1 and the WCRModule-2, anterior and posterior frame segments respectively, said mechanical devices for said contact include at least one mechanical switch, line-cord mechanisms capable of executing processes for effectuating said mechanisms for the contact and the bracing interval of the protective helmet and the vest/torso bracing framework component against said exterior impacts, without utilization of an electrical power sourcing implement, c. said bracing interval for momentary cessation of independent movement and a mechanically fortifying means for instantaneous rendering as rigid said array such that it will effectuate a solid, inflexible, but momentary wall-like structure for said frame thereby rendering the torso/spinal cord of the wearer of the apparatus less vulnerable to injuries that may arise from said exterior impacts against the vest/torso bracing framework component;
 6. The body impact bracing apparatus of claim 1 wherein said collar/shoulder bracing component includes: a. the neck stabilizing and spanning device for bracing between the helmet and said shoulder guard harness, latter said spanning device includes mechanical, non-electronic clenching elements, said friction and anchoring/controlling rods for means of processes of said bracing, b. the harnessing and position sensing device for the helmet, c. a clamping device for securitization of said helmet onto the harnessing and position sensing device, d. said buttressing device for supporting the weight of said helmet on the head of the wearer of the apparatus, e. a mechanical means for impetus of bracing of the collar/shoulder bracing component consequent to said exterior impacts against both the shoulder guard harness and the protective helmet, f. said lateral movement/flex damper device for damping any counter movement of the head of the wearer against any side of interior wall surface of the protective helmet;
 7. The body impact bracing apparatus of claim 1 wherein said collar/shoulder bracing component and said vest/torso bracing framework component are both involved with electrical and mechanical, coordinated, and corresponding means for processes of said bracing due to said exterior impacts against said protective helmet of the collar/shoulder bracing component and said vest/torso bracing framework component, such that the collar/shoulder bracing component would receive said immediate, and reciprocal onset-of-impact bracing signals originating from both the protective helmet or the vest/torso bracing framework component, further such that said vest/torso bracing framework component would receive said immediate and reciprocal onset-of-impact bracing signals originating from both the protective helmet and the vest/torso bracing framework component itself; both the collar/shoulder bracing component, together with the protective helmet, and the vest/torso bracing framework component are mutually inter-reactive, mutually protective, operating mainly as a two-component, integrated, tandem system, the apparatus, working in unison as a singular cooperative unit, against injurious impacts;
 8. The body impact bracing apparatus of claim 5 wherein said mechanical devices for said contact is operative within said collar/shoulder bracing component such that the collar/shoulder bracing component may operate exclusive of electrical processes; accordingly, the collar/shoulder bracing component would immobilize any measure of movement of the protective helmet thereby circumventing injury to both the head and neck of said wearer of the body impact bracing apparatus, said collar/shoulder bracing component thus providing an anchoring and stabilizing means for said protective helmet against said external impacts;
 9. The body impact bracing apparatus of claim 1 wherein said collar/shoulder bracing component and said signal transmission means involve both electrical and mechanical processes for means of said bracing of the collar/shoulder bracing component itself with its harnessing and position sensing device thus achieving the objective said bracing for protection of the head and neck segments, exclusive of torso segment, upon said onset-of-impact bracing signals from the protective helmet and from the shoulder guard harness of said collar/shoulder bracing component, latter said bracing entails that, at least: a. an onset-of-impact bracing signal will correspond with said neck stabilizing and spanning device of the apparatus causing said collar/shoulder bracing component to brace, b. a structural assembly of said friction and anchoring/controlling rods of the neck stabilizing and spanning device is predetermined for process of said bracing upon said onset-of-impact bracing signals arising from said impact against said protective helmet or against said vest/torso bracing framework component thus further protecting the neck and head against said external impact, c. the harnessing and position sensing device of said collar/shoulder bracing component will initiate upon being moved off its center configuration by a jolt from said exterior impact to the protective helmet, or to the shoulder guard harness;
 10. The body impact bracing apparatus of claim 3 wherein said array is disposed between at least two layers of said torso bracing jacket, within the vest/torso bracing framework component, and, further contained and partitioned in its processes, there being at least a protective sheath closest to the wearer's body so that the operations of said vest/torso bracing framework component are inhibited from direct and adverse physical contact with the body of the wearer, said vest/torso bracing framework component materially consisting of layers of at least durable and semi-rigid fabrics that are predetermined for sustained forceful and robust field usage against wear, tear, stress, and breakage presumed in sports activities such as hockey, American football, and even rodeo bull riding competitions such, said fabrics being designed to allow contoured ease-of-movement for both wearer and for the vest/torso bracing framework component itself; whereby, in sports activities such as hockey, American football, rugby, rodeo bull riding, etc., said wearer of the apparatus would be capable of deflecting potentially injurious field impacts of force without the usual results of traumatic and incapacitating injuries to the head and torso, but more importantly, to the neck, which has been generally overlooked in concussive, TBI/CTE injury determinations; the neck, the upper cervix spine, and Atlas vertebra, are the most vulnerable segment between the head and the torso with respect to impact injuries, according to medical specialists; so, any impact to the helmet/head in hockey and American football, and any punch to the face/head in boxing will be adversely registered both in the brain and by the neck, cumulatively; the most muscular of necks cannot protect against unforeseen, split-second offensive impacts; accordingly, the mid-segment “bracing bridge,” the neck stabilizing and spanning device between the head and torso is introduced; it instantaneously stabilizes impacting movements of the head and torso from either falls or from lateral offensive impacts, such tandem bracing device, being so integrally-positioned is the focal point and central protective means for the body impact bracing apparatus without which, and continuing to use flawed conventional protective gear, debilitating and fatal health issues will continue.
 11. A method of using a body impact bracing apparatus, comprising the steps: a. securely donning a collar/shoulder bracing component for a protective helmet for means of bracing protection against possible external impact injuries to the head, neck, or torso of a wearer of the body impact bracing apparatus, said collar/shoulder bracing component includes:
 1. a neck stabilizing and spanning device for bracing between the helmet and a vest/torso bracing framework component,
 2. a harnessing and position sensing device for the helmet,
 3. a clamping device for securitization of said helmet onto the head of a wearer of the harnessing and position sensing device,
 4. a buttressing device for supporting the weight of said helmet on the head of the wearer of the apparatus,
 5. a lateral movement/flex damper device for damping any counter movement of the head of the wearer against any side of interior wall surface of the protective helmet,
 6. a shoulder guard harness with its respective means for onset-of-impact bracing signals to both the protective helmet and to the vest/torso bracing framework component, said shoulder guard harness being further stabilized by tubing which, itself is structurally supported by a strapping facility being secured by a strapping means at the waist of the wearer; b. securely donning and strapping into place the vest/torso bracing framework component for means of protection against said possible external impacts to the head, neck, and torso of the wearer of the apparatus, said apparatus providing protective means such that said collar/shoulder bracing component and said vest/torso bracing framework component are predisposed for inter-dependent bracing thus constituting a mutually dependent means of the apparatus for enclosing, thus protecting, the central nervous system of the human body, head, neck, and torso/spinal cord, from injurious impacts, said system extending from the head to below the torso waist; accordingly, neither of said collar/shoulder bracing component nor of the vest/torso bracing framework component, being exclusive with respect to the onset-of-impact bracing signals arising from either component, so necessarily providing inter-reactive means for mutual bracing protection as a two-component apparatus means for operating in unison for total protection of head, neck and torso/spinal cord members; c. then said wearer, being so protected, exposing the apparatus, being thus worn, to known, but unpredictable and potentially injurious occasions of aggressive forces from said external impacts, said apparatus employing at least one signal transmission means for inter-reactive correspondences of onset-of-impact bracing signals for cessation of movement arising from said external impacts against said protective helmet of the collar/shoulder bracing component and against said vest/torso bracing framework component of the apparatus;
 12. The method of using the body impact bracing apparatus of claim 11 wherein said neck stabilizing and spanning device being a linking, inter-component, process whereby said collar/shoulder bracing component and said vest/torso bracing framework component are predisposed for bracing with respect to each other for an interval, said bracing being due to said onset-of-impact bracing signals arising from said external impacts against the head, neck, or torso; said spanning device of the collar/shoulder bracing component, therefore, is central to the apparatus, providing a contiguous, tandem-bracing relationship between: a. upper and lower components of the apparatus, which are the collar/shoulder bracing component and the vest/torso bracing framework component, respectively, and b. a first component means and a second component means for their corresponding protective bracing of:
 1. Head,
 2. Neck, and
 3. Torso, thus being a three-segment exposure to injury requiring a three-segment protective apparatus in two components, neither component working in isolation, without the other, for complete protection of the CNS as a whole: head, neck, and torso/spinal cord, each being suspect upon medical assessments due to concussion impact determinations; whereby, the 3-segment dual component protective focus of the bracing apparatus solves a major problem by providing protective means against impact injuries, not just to the head within a faulty protective helmet but, more importantly with this new technology, to the neck: the cervix section of the vertebral column, which continues extending downward through the torso to below the waist; accordingly, the design of such dual component apparatus presumes the integrity, the entirety, of the Central Nervous System, any part of which being damaged, at least by concussive impacts, can cause subtle but cumulative withdrawals of vital elements for neurological health thus rendering those wearing flawed conventional protective equipment vulnerable to likely debilitating neurological diseases, TBI/CTE, (Traumatic Brain Injury & Chronic Traumatic Encephalopathy) which too often, in hockey and American football alone, result in serious behavioral problems, memory loss, other long-term health issues, referred to as post concussion syndrome, PCS; its symptoms, from even mild head injury, include: headache, dizziness, fatigue, poor memory, poor concentration, irritability, depression, sleep disturbance, frustration, restlessness, sensitivity to noise, blurred vision, double vision, photophobia, nausea, tinnitus, and others; recovery can take weeks or months, some of these can become chronic; medical research has found that cumulative concussions may lead even to death as related to, or subsequent to, the above as causative factors; medical research has also found that impact concussions, being too often misdiagnosed as a problem in the head, must be attributed to the head, neck, (cervix) and spinal cord, which are, per se, the confines of the central nervous system, for which the Body Impact Bracing Apparatus seeks to provide integral adequate protection. 